US2905841A - High power x-ray tube with membrane anode - Google Patents

High power x-ray tube with membrane anode Download PDF

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Publication number
US2905841A
US2905841A US632160A US63216057A US2905841A US 2905841 A US2905841 A US 2905841A US 632160 A US632160 A US 632160A US 63216057 A US63216057 A US 63216057A US 2905841 A US2905841 A US 2905841A
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United States
Prior art keywords
anode
cooling
membrane
ray tube
channels
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Expired - Lifetime
Application number
US632160A
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English (en)
Inventor
Meyer Konrad
Hummel Gerhard
Ewert Heinz
Hofmann Ernst Gunter
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Licentia Patent Verwaltungs GmbH
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Licentia Patent Verwaltungs GmbH
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    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/02—Details

Definitions

  • the anode consists .of .a thin sheet of metal forming .a part of .the casing of t he X-ray tube.
  • This membrane anode must, however, be :provided with highly efiicient cooling means, since the greater part of the energy of the electrons impinging upon the anode target .is converted into heat rather than X-rays.
  • a waste of energy is avoided by'the X-ray tube of the invention by adapting the load applied to the anode to the particular requirements of the object to be treated with X-rays. This is accomplished by providing means for adapting and directing the stream of electrons within the X-ray tube to a surface .of the cooled anode membrane corresponding to the desired held of radiation. Therefore only those areas of the large membrane are supplied with impinging electrons which are actually needed for producing the radiation required at any particular moment and for a specific purpose.
  • objects of various sizes and dimensions can be subjected to the ,ra-
  • FIG. 2 is another diagram of one embodiment of the cooling channel of the invention and shows the advantages of the present invention
  • Figure 3 is a cross-sectional view ofthe cooling channels for the X-ray tube of the invention.
  • Figure 4 is a cross-sectional view-of another embodiment of the cooling channels for the X-ray tube of the invention.
  • Figure '5 is a cross-sectional view of still another embodiment of the cooling channels 'for the X-ray tube of the invention.
  • Figure 6 is a cross-sectional view of a preferred ,embodiment of the cooling channels for the X-ray tube of the invention.
  • Figure'7 is a diagram showing'the direction of'flow of'the cooling liquid within the cooling channel shown "in Figures 3 to 6;
  • Figure 8 is a cross-sectional view of one embodiment of the X-ray tube of the invention.
  • Figure 9 is a longitudinal sectional view of theembodirnent of 'the X-ray tube of the invention shown in Figure 8; v
  • Fig. 10 is a longitudinal sectional viewsimilar to Fig. 9 butshowing another embodiment of a cathode assembly
  • Fig. 11 is a longitudinal sectional view similar "to 3 Figs. 9a'nd 10 but showing still another embodiment of a cathode assembly.
  • Fig. 12 is a fragmentary cross-sectional view of yet another embodiment of a cathode assembly.
  • the ray-transmissive membrane anode 2 is fastened at the casing wall 1.
  • a corrugated body 3 is mounted upon the membrane anode and thereby several tubular channels are formed.
  • the cooling means flows through these tubular channels in a vertical direction relative to the plane of Figure 3.
  • tubular channels do not contact each other directly. They are connected to each other by solid bridges 5 which can, for example, be welded to the adjoining channel walls. In this case it is advantageous to choose bridges having a width which is greater than the combined width of the anode membrane at the wallof the body 3.
  • the lens shaped construction of the cooling channels has proved to be of great advantage.
  • the channels are preferably constructed of a thin material absorbing only a small portion of the X-rays, as for example aluminum or plastics.
  • the structure of the channels also results in a mechanical stabilization of the membrane anode.
  • the channels can be thinly coated with a heavy metal e.g. gold.
  • focal streak a focal spot having the form of a streak 4 (hereinafter called focal streak) can be created upon the anode portion of each cooling channel.
  • the energy of the various focal streaks may vary, but the energy must be equally and evenly distributed across the entire focal streak, if a regular and even radiation is to be achieved.
  • the object to be subjected to the radiation of the X-ray tube must of course be moved in a vertical direction to the focal streaks.
  • the adaptation of the stream of electrons to the desired field of radiation can be effected by providing a number of different cathode and/or anode assemblies which can be exchanged at will. Thereby the field of radiation can be varied and adapted to the requisite purpose.
  • Tubes of this kind are usually constantly evacuated during their operation by a system of vacuum pumps. Preferably they work at an operational voltage of from 100 to 250 kv.
  • the X-ray tube of the invention is equipped with electro-optical means causing particular heating filaments or particular portions of the heating filaments not to emit electrons towards those parts of the membrane anode which are not needed for the particular purpose.
  • certain portions of the heating filaments can be electro-statically screened against the anode by screens having the cathode potential.
  • no X-rays are created upon the corresponding portions of the membrane anode.
  • the energy of the stream of electrons is thus used solely for creating X-rays upon that portion of the anode membrane which is needed for the radiation to be applied to the particular object.
  • the heating filaments can be subdivided and/or provided with supply wires or taps which are guided out of the X-ray tube separately and isolated from each other.
  • the size and the configuration of the field of radiation of the X-ray tube can be varied from the outside by switching in the corresponding portion of the heating filaments.
  • several heating filaments can be connected in series or in parallel in groups. In that case one or several of the groups can be switched in at will. It is also possible to combine both switching arrangements just indicated.
  • the cathode elements there may be arranged one or several heating filaments.
  • Every cathode element used for creating a focal spot is screened against the other cathode elements and is electro-statically caused to create the desired focal streak upon the membrane anode.
  • the heating filaments of the cathode elements can be connected in parallel or in series either singly or in groups.
  • the X-ray tube is preferably constantly evacuated.
  • the anode is loaded with several focal streaks each produced by a cathode element. A separate cooling channel is provided for each focal streak.
  • the mem brane anode 22 is exchangeably fastened at thetube wall 21 by means of a screw 24, sealing means 23 being interposed.
  • the membrane anode is of a corrugated shape. In front of the latter there are located the cooling channels 25, the walls 26 of which are also corrugated.
  • the cooling liquid is supplied through pipe section 27 and removed through pipe section 28.
  • the casing wall 21 consists of a metal as, for instance, copper or a ceramic material.
  • the cathode assembly 29, which may be isolated, is exchangeably fastened at the wall 21 of the casing by means of screw 30.
  • the cathode assembly comprises a plurality of parallel positioned, heating filaments 31 which are separated from each other 'by screen 32. These screens are so arranged that the electrons emitted by any particular of the heating filaments 31 impinge only upon the crest of the corresponding corrugation of the membrane anode.
  • two additional cooling pipes which have no corresponding cathode.
  • the heating filament 31 of the cath ode element consists of one single coiled wire.
  • the cathode assembly can be exchanged for another cathode assembly after the anode assembly which includes the anode membrane has been removed, the removal of the anode and cathode assemblies being made possible by unscrewing the screws 24, 30.
  • the single cathode elements may have a greater number or shorter or differently connected heating wires (for example con nected in series) which may be at will switched off singly or in groups, each group comprising several Wires.
  • Fig. 11 wherein the tube wall is indicated at 211), the membrane anode at 22b, and the filaments at 3112.
  • a cathode assembly such as is shown in Fig. 10 may be substituted.
  • the tube wall is indicated at 21a
  • the filaments 31a are screened by electrostatic screens 33 which can be welded or soldered to the cathode assembly 36 in any desired adjusted position. In this way, the screens will be at cathode potential.
  • the cathode assembly may, as fragmentarily shown in Fig.
  • the anodes of the embodiments of the X-ray tube of the invention just described canbe subjected toaa high specific load, so that in case of equilibrium the anode asvsumes a temperature of 300 degrees centigrade.
  • the cooling can be effected in the way of the generallyknown vapor cooling. If this cooling method is employed it is imperative to remove the resulting steam bubbles from the anode as quickly as possible by a highwater pressure and a turbulent current ofthe coolingliquid. '(Reynolds number in excess of 10,000). If this is done,- an energy of at least 750 watts jec.
  • a high power high-tension X-ray tube comprising a ray-transmissive membrane anode which operates at a temperature of the order of 300 degrees centigrade and a cooling system for cooling said anode, said cooling system comprising a plurality of cooling channels for circulation of cooling liquid therein, said cooling channels being arranged parallel to each other, said membrane anode forming an integral part of said cooling channels.
  • a high power high-tension X-ray tube comprising -a ray-transmissive membrane anode which operates at a temperature of the order of 300 degrees centigrade. and :a cooling systemtor cooling said anode, said cooling ,sys
  • cooling channels tem comprising a plurality of cooling channels'for circulation of cooling liquid'therein, .said cooling channels being arranged parallel toeac'h other, said cooling channels :being formed by saidanode membrane and byanioutjer wall, said membrane anode beingplanar and said outer wall being corrugated, said outer wall and said-membrane .anode'being joined to form said-cooling channels.
  • a high power high-tension X-ray tube comprising araY-transniissive membraneanode which operates 'at a -:ternperature of the order. of 30.0 degrees centigradeand :a
  • cooling system for cooling said anode, said cooling ,system comprising a plurality of cooling channels for circulation of cooling liquid therein, said cooling channels being arranged parallel to each other, said cooling :.channels being formed by said anode membrane and by an -outer wall, said membrane anode: being corrugated and said outer wall being planar, said outer wall and said membrane anodebeiug joined to:form said cooling channels.
  • a high power high-tension X-ray tube comprising a vray transinissive membrane anode which operates at a temperature ofthe order of 300degrees centigrade and a cooling system for cooling said anode, saidcooling system comprising a plurality of cooling channels for circulation of coolingliquid therein, saidcooling channelslbeing arranged parallel to each other, said cooling channels being formed by saidanode membrane andby .an outer wall,
  • said membrane anode and said outer wall being corrugated, said membrane anode and said outer wall being joined to form said coolingchannels.
  • a high power high-tension X-ray tube comprising a ray-transmissive membrane anode which operates at .a temperature of the order of 300 degrees centigrade and a cooling system for cooling said anode, said cooling system comprising a plurality of cooling channels for circulation of cooling liquid therein, said cooling channels being arranged parallel to each other, said cooling channels being formed by said anode membrane, by said outer wall and by aplurality ofibridges, said membrane anode and said outer wall being corrugated, said :membrane anode and said outer wall being joined to formsaidchannels and said bridges separating each of said channels from theadjoining channels.
  • a high powerhigh-tension X-ray tube comprising a ray-transmissive membrane anode which operates at -a temperature of'theorder-of 300 degrees'centigrade and a cooling system for cooling said anode, said cooling system comprising a plurality of cooling channels for circulation of cooling liquid therein, said cooling channels being arranged parallel to each other, said cooling channels being formed by said anode membrane, by said outer wall and by a plurality of bridges, said bridges having a thickness which is greater than the combined thickness of said anode membrane and said outer wall, said membrane anode and said outer wall being corrugated, said membrane anode and said outer wall being joined to form said channels and said bridges separating each of said channels from the adjoining channels.
  • a high power high-tension X-ray tube comprising a ray-transmissive membrane anode which operates at a temperature of the order of 300 degrees centigrade and a cooling system for cooling said anode, said cooling system comprising a plurality of cooling channels for circulation of cooling liquid therein, said cooling channels being arranged parallel to each other, said cooling channels being formed by said anode membrane and by an outer wall, said membrane anode and said outer wall being joined to form said cooling channels, said cooling channels being provided at their respective sides inside the vacuum of said X-ray tube with a thin layer of heavy metal.
  • a high power high-tension X-ray tube comprising a ray-transmissive membrane anode which operates at a temperature of the order of 300 degrees centigrade and a cooling system for cooling said anode, said cooling system comprising a plurality of cooling channels for circulation of cooling liquid therein, said cooling channels being arranged parallel to each other, said cooling channels being formed by said anode membrane and by an outer wall, said membrane anode and said outer Wall being joined to form said cooling channels, said cooling channels being provided at their respective sides inside the vacuum of said X-ray tube with a thin layer of gold.
  • a high power high-tension X-ray tube comprising a ray-transmissive membrane anode which operates at a temperature of the order of 300 degrees centigrade and a cooling system for cooling said anode, said cooling system comprising a plurality of cooling channels for circulation of cooling liquid therein, said cooling channels being arranged parallel to each other, said membrane anode forming an integral part of said cooling channels, and means for imparting an elevated speed. to said cooling liquid within said cooling channels that a turbulent current is formed.
  • a high power high-tension X-ray tube comprising a ray-transmissive membrane anode which operates at a temperature of the order of 300 degrees centigrade and a cooling system for cooling said anode, said cooling system comprising a plurality of cooling channels for circulation of cooling liquid therein, said cooling channels being arranged parallel to each other, said membrane anode forming an integral part of said cooling channels, and means for creating a separate focal spot for each of said cooling channels.
  • a high power high-tension X-ray tube comprising 7 of said membrane anode which are cooled by said pluof said cathode assembly with a view to supply an area of said'membrane anode with a stream of impinging electrons which is suflicient to produce a desired field ofradiationof X-rays.
  • a high-power high-tension X-ray tube comprisin an anode assembly including a ray-transmissive membrane anode which operates at a temperature of the order of 300 degrees centigrade, a cooling system for cooling said membrane anode, said cooling system including a plurality of cooling channels for circulation of cooling liquid therein, said cooling channels being arranged parallel to each other, said membrane anode forming an integral part of said cooling channels, a cathode assembly including a plurality of heating filaments emitting electrons when heated for creating separate focal spots on those areas of said membrane anode which are cooled by said plurality of cooling channels, respectively, and electrooptical means for restricting the stream of electrons emitted by said filaments to an area of said membrane anode sutficient to produce a desired field of radiation of X rays, said electro-optical means including a plurality of adjustable screens at cathode potential for electrostatically screening various portions of said heating filaments against said membrane anode.
  • cathode assembly comprises a plurality of cathode elements, said cathode elements being positioned parallel relative to each other, each of said cathode elements being provided with at least one of saidheating filaments, each of said cathode elements influencing its corresponding wire so as to produce each one focal streak, and means for switching in from the outside any of said heating filaments singly or in combination.

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  • X-Ray Techniques (AREA)
US632160A 1956-01-02 1957-01-02 High power x-ray tube with membrane anode Expired - Lifetime US2905841A (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DEL21680A DE1033343B (de) 1956-01-02 1956-01-02 Roentgenroehre hoher Strahlungsleistung
DE850312X 1956-01-02

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CH (1) CH342664A (de)
DE (1) DE1033343B (de)
GB (1) GB850312A (de)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE1191498B (de) * 1960-04-11 1965-04-22 Licentia Gmbh Hochstromroentgenroehre mit Aussenanode
US3267315A (en) * 1962-06-05 1966-08-16 Licentia Gmbh X-ray source comprising plural removable modular units each having an anode targetand cathode
US3296476A (en) * 1961-10-31 1967-01-03 Licentia Gmbh X-ray tube
US3601647A (en) * 1969-02-27 1971-08-24 Rca Corp High power electron discharge device having anode with improved heat dissipation capability
US4035685A (en) * 1974-04-11 1977-07-12 U.S. Philips Corporation Solid cathode cap for an X-ray tube
US4340816A (en) * 1976-10-19 1982-07-20 Siemens Aktiengesellschaft Method of producing tomograms with x-rays or similarly penetrating radiation
US4349740A (en) * 1976-12-23 1982-09-14 Siemens Aktiengesellschaft Apparatus for displaying fluoroscopic tomographic images of the body
US20090041198A1 (en) * 2007-08-07 2009-02-12 General Electric Company Highly collimated and temporally variable x-ray beams
ITVR20100016A1 (it) * 2010-02-02 2011-08-03 Microtec Srl Tubo radiogeno
JP2018190526A (ja) * 2017-04-28 2018-11-29 浜松ホトニクス株式会社 Ｘ線管及びｘ線発生装置

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2024039669A1 (en) * 2022-08-19 2024-02-22 Canazon John X-ray tube with corrugated wall

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2329318A (en) * 1941-09-08 1943-09-14 Gen Electric X Ray Corp X-ray generator
US2517260A (en) * 1945-09-18 1950-08-01 Research Corp Apparatus for generating an accurately focused beam of charged particles and for related purposes
US2729748A (en) * 1950-08-17 1956-01-03 High Voltage Engineering Corp Apparatus for sterilizing foods, drugs and other substances by scanning action of high-energy electrons

Family Cites Families (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE532773C (de) * 1931-09-02 C H F Mueller Akt Ges Roentgenroehre fuer Weichstrahlung
DE588522C (de) * 1933-11-18 Siemens Reiniger Werke Akt Ges Roentgenroehre, bei der der Antikathode eine auf Antikathodenpotential befindliche Blende vorgelagert ist, zur Erzeugung eines laenglichen Brennfleckes
DE321952C (de) * 1918-04-26 1920-06-15 Siemens & Halske Akt Ges Roentgenroehre mit einer in die Glaswandung eingesetzten, von aussen gekuehlten Antikathode
CH103540A (de) * 1922-01-14 1924-02-16 C H F Mueller Fa Einrichtung zur Auslösung von Kathodenstrahlen.
DE586817C (de) * 1930-12-11 1933-10-26 Radiologie Akt Ges Verfahren zur Brennfleckregelung fuer Roentgenroehren durch Veraenderung der emittierenden Gluehkathodenflaeche
DE683559C (de) * 1932-12-21 1939-11-09 Radiologie Akt Ges Roentgenroehre mit dreidimensional gewickelter Gluehkathode
DE690618C (de) * 1937-01-19 1940-04-30 Siemens Reiniger Werke Akt Ges Einrichtung zur Erzeugung eines konvergenten Roentgenstrahlenbuendels
FR927971A (fr) * 1946-04-26 1947-11-14 Radiologie Cie Gle Tubes à rayons x pour endothérapie des cavités naturelles
DE934002C (de) * 1952-02-20 1955-10-06 Licentia Gmbh Strahlenaustrittsfenster fuer Roentgenroehren, Elektronenroehren und andere elektrische Entladungsgefaesse

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2329318A (en) * 1941-09-08 1943-09-14 Gen Electric X Ray Corp X-ray generator
US2517260A (en) * 1945-09-18 1950-08-01 Research Corp Apparatus for generating an accurately focused beam of charged particles and for related purposes
US2729748A (en) * 1950-08-17 1956-01-03 High Voltage Engineering Corp Apparatus for sterilizing foods, drugs and other substances by scanning action of high-energy electrons

Cited By (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE1191498B (de) * 1960-04-11 1965-04-22 Licentia Gmbh Hochstromroentgenroehre mit Aussenanode
US3296476A (en) * 1961-10-31 1967-01-03 Licentia Gmbh X-ray tube
US3267315A (en) * 1962-06-05 1966-08-16 Licentia Gmbh X-ray source comprising plural removable modular units each having an anode targetand cathode
US3601647A (en) * 1969-02-27 1971-08-24 Rca Corp High power electron discharge device having anode with improved heat dissipation capability
US4035685A (en) * 1974-04-11 1977-07-12 U.S. Philips Corporation Solid cathode cap for an X-ray tube
US4340816A (en) * 1976-10-19 1982-07-20 Siemens Aktiengesellschaft Method of producing tomograms with x-rays or similarly penetrating radiation
US4349740A (en) * 1976-12-23 1982-09-14 Siemens Aktiengesellschaft Apparatus for displaying fluoroscopic tomographic images of the body
US20090041198A1 (en) * 2007-08-07 2009-02-12 General Electric Company Highly collimated and temporally variable x-ray beams
ITVR20100016A1 (it) * 2010-02-02 2011-08-03 Microtec Srl Tubo radiogeno
WO2011095925A1 (en) * 2010-02-02 2011-08-11 Microtec S.R.L. X-ray tube
JP2018190526A (ja) * 2017-04-28 2018-11-29 浜松ホトニクス株式会社 Ｘ線管及びｘ線発生装置
CN110582831A (zh) * 2017-04-28 2019-12-17 浜松光子学株式会社 X射线管和x射线产生装置
KR20200002784A (ko) * 2017-04-28 2020-01-08 하마마츠 포토닉스 가부시키가이샤 X선관 및 x선 발생 장치
EP3618093A4 (de) * 2017-04-28 2021-01-06 Hamamatsu Photonics K.K. Röntgenröhre und röntgenstrahlerzeugungsvorrichtung
US11004646B2 (en) 2017-04-28 2021-05-11 Hamamatsu Photonics K.K. X-ray tube and X-ray generation device
CN110582831B (zh) * 2017-04-28 2022-03-04 浜松光子学株式会社 X射线管和x射线产生装置

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CH342664A (de) 1959-11-30
GB850312A (en) 1960-10-05
DE1033343B (de) 1958-07-03

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