CN109698105A - The transmission and reflectance target x-ray system and application method of high dose output - Google Patents

The transmission and reflectance target x-ray system and application method of high dose output Download PDF

Info

Publication number
CN109698105A
CN109698105A CN201811234524.1A CN201811234524A CN109698105A CN 109698105 A CN109698105 A CN 109698105A CN 201811234524 A CN201811234524 A CN 201811234524A CN 109698105 A CN109698105 A CN 109698105A
Authority
CN
China
Prior art keywords
target
ray tube
ray
anode
construction
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.)
Granted
Application number
CN201811234524.1A
Other languages
Chinese (zh)
Other versions
CN109698105B (en
Inventor
菲利浦·肯特·奥斯本
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.)
Pull Deyuan Technology Co Ltd
Original Assignee
Pull Deyuan Technology Co 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.)
Filing date
Publication date
Priority claimed from US15/709,426 external-priority patent/US11101096B2/en
Application filed by Pull Deyuan Technology Co Ltd filed Critical Pull Deyuan Technology Co Ltd
Publication of CN109698105A publication Critical patent/CN109698105A/en
Application granted granted Critical
Publication of CN109698105B publication Critical patent/CN109698105B/en
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Classifications

    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/24—Tubes wherein the point of impact of the cathode ray on the anode or anticathode is movable relative to the surface thereof
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/02—Details
    • H01J35/16—Vessels; Containers; Shields associated therewith
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/24—Tubes wherein the point of impact of the cathode ray on the anode or anticathode is movable relative to the surface thereof
    • H01J35/30—Tubes wherein the point of impact of the cathode ray on the anode or anticathode is movable relative to the surface thereof by deflection of the cathode ray
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J9/00—Apparatus or processes specially adapted for the manufacture, installation, removal, maintenance of electric discharge tubes, discharge lamps, or parts thereof; Recovery of material from discharge tubes or lamps
    • H01J9/02—Manufacture of electrodes or electrode systems
    • H01J9/18—Assembling together the component parts of electrode systems
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J9/00—Apparatus or processes specially adapted for the manufacture, installation, removal, maintenance of electric discharge tubes, discharge lamps, or parts thereof; Recovery of material from discharge tubes or lamps
    • H01J9/24—Manufacture or joining of vessels, leading-in conductors or bases
    • H01J9/26—Sealing together parts of vessels

Landscapes

  • Engineering & Computer Science (AREA)
  • Manufacturing & Machinery (AREA)
  • X-Ray Techniques (AREA)

Abstract

The transmission of high dose output and the target X-ray tube and application method of reflection generally comprise the X-ray tube for being accelerated under high-voltage potential to electronics, include the High Pressure Shell of evacuation；The target anode of hemispherical transmission and reflection is arranged in the shell；Cathode construction, for making electronics towards the hemispherical anode deflection being arranged in the shell；Filament is located at the geometric center for the anode hemisphere being arranged in the shell；Power supply is connected to the cathode to provide acceleration voltage to electronics.

Description

The transmission and reflectance target x-ray system and application method of high dose output
Cross reference to related applications
In allowed by law full breadth, the application of this U.S. Non-provisional Patent be submit on December 31st, 2014 by Entitled " High Dose Output, the Through Transmission Target X-Ray of assigned sequence number 14/587,634 The continuation part of the U.S. Non-provisional Patent application of System and Methods of Use " requires its priority and complete hereby The equity in portion.
Technical field
The disclosure relates generally to X-ray Manifold technologies, and relate more particularly to that there is specific anode, cathode, filament to match Set and material selection X-ray tube, with generate high dose X-ray output.
Background technique
In many typicalness of prior art X-ray tube, cathode assembly and anode assemblies are in glass or Metal Packaging It (envelope) is vacuum-packed in.Electronics is generated by least one cathode filament in cathode assembly.These electronics pass through High voltage electric field accelerates towards anode assemblies.High energy electron generates X-ray when hitting with anode assemblies.The by-product of the process is Generate a large amount of heat.
Traditional X-ray tube configuration be in the prior art it is known, for example, Coolidge type X-ray tube.? In Coolidge pipe, being shown as an x-ray photon for output radiation mode is hit by the electron beam that will go out from filament emission It is generated on to the surface of target anode.Coolidge pipe can be with single-ended operation, and wherein cathode is in negative potential and anode It is operated in ground connection or both-end, wherein cathode is in negative potential and anode is in positive potential.In any configuration, add The energy of speed is the difference between electrode potential.In Coolidge X-ray tube, target anode is by such as tungsten, tantalum or iridium Heavy metal is made, and the density and high-melting-point due to this material and select this material.The material of target anode is most frequently It is installed on Heat Conduction Material (such as copper) and by cooling outside water or dielectric oil.
Target anode and electron beam are in line placements, and radiation with electron beam angle at right angle to be emitted.It is defeated The spectrum radiated out is mainly bremsstrahlung, and the acceleration energy by changing electron beam changes.This property it is effective In industrial imaging, medical imaging, analysis and radiation application.The major limitation of such pipe is the target before fusing occurs The watt density of anode loads, the limited utilization of x-ray photon generated and the symmetry of gained radiation field.Because of imaging The resolution ratio of equipment (electronic device or film) is the function for projecting the electron beam dimensions on target anode.For optimized image Resolution ratio needs small focus, but is directed to optimized image contrast, needs a large amount of x-ray photon.The two requirements are opposite And can not be solved in traditional pipe design.In addition, the reflectivity properties of transmitting radiation are asymmetric about beam center line, and And it is very inefficient for being directed to X-ray radiation application.
Recently, transmission (through transmission) X-ray tube of some low-power goes out on the market It sells.These pipes use individual element (element) as composite object and output window.The most frequently used element is tungsten, this It is but cost to be reduced to radiant output because of its higher fusing point.
It is therefore evident that in the presence of the identifiable unsatisfied demand exported to high dose, transmission target X Ray system and application method radiate with biggish surface area anode target and therefore realize higher atomic number number Material is marked, there is improved radiant output, lower fusing point and higher evaporating pressure and is generated needed for higher output radiation Low electrode current potential.
Summary of the invention
It compactly describes, in the exemplary embodiment, the present apparatus overcomes shortcomings noted above and meets to high agent Measure the generally acknowledged demand of output, transmission target X-ray tube and application method generally include under high-voltage potential to electronics The X-ray tube of acceleration, the X-ray tube include: the evacuation shell sealed；Transmission mesh on the housing is set Anode construction is marked, the anode construction is configured with the hemispherical of geometric center；The cathode being arranged in the shell Structure, the cathode are configured as deflecting electronics towards the hemispherical anode；The filament being arranged in the shell, institute It states filament and is positioned proximate to the hemispheric geometric center and between the anode and the cathode；Evacuate shell Body, the shell are configured as vacuum there and enclose the anode, the cathode and the filament, and therefore, this X is penetrated Spool, which is used as, provides large surface area anode target to radiate, and is able to use different z materials using with improved spoke Penetrate the characteristic X-ray of output, more low melting point and lower electrode current potential needed for generating higher output radiation.
According to its main aspect and statement extensively, the transmission target X-ray tube and application method of high dose output are total Include the X-ray tube for accelerating under high-voltage potential to electronics on body, includes evacuation High Pressure Shell；Hemispherical transmission passes Defeated target anode is arranged in the shell；Cathode construction makes electronics towards the hemispherical sun being arranged in the shell Pole deflection；Filament, positioned at the geometric center for the anode hemisphere being arranged in the shell；Power supply, be connected to the cathode with Acceleration voltage is provided to electronics.
In the exemplary embodiment of transmission target X-ray tube and application method, X-ray tube includes: to be sealed Evacuate shell；The transmission target anode structure being arranged on shell, anode construction are configured with geometric center Hemispherical；Cathode construction in the housing is set, cathode is configured as deflecting electronics towards anode construction；It is arranged on shell Filament in body, filament are positioned proximate to hemispheric geometric center and between the anode and cathode, wherein evacuating shell quilt It is configured to make anode construction, cathode construction and filament vacuum sealing wherein.
For under high-voltage potential to another example of the electronics transmission accelerated and reflectance target X-ray tube In property embodiment, comprising: shell；The transmission and transmission and reflection target anode structure, anode construction being arranged on shell are matched It is set to the hemispherical at the center with the circle created by 2D substrate；Cathode construction in the housing is set, cathode construction is matched Being set to deflects electronics towards anode construction；Filament in the housing is set, filament is positioned proximate to by hemispheric 2D Substrate creation circle center and between anode construction and cathode construction, wherein evacuate shell be configured as making anode wherein Structure, cathode construction and filament vacuum sealing.
In the exemplary embodiment of transmission target X-ray tube, for generating the method packet of monochromatic output X-ray spectrum The step of X-ray tube for being accelerated under high-voltage potential to electronics is provided is included, which includes the pumping sealed Empty capsid；The transmission and transmission and reflection target anode structure, anode construction being arranged on shell are configured in geometry The hemispherical of the heart；Cathode construction in the housing is set, cathode construction is configured as deflecting electronics towards anode construction；Quilt Filament in the housing is set, and filament is positioned proximate to the center of the circle created by hemispheric 2D substrate and in anode construction Between cathode construction, wherein directly being contacted by the circle that hemispheric 2D substrate creates with cathode construction, and shell is wherein evacuated Body is configured as making anode construction, cathode construction and filament vacuum sealing wherein, to only lower than at least one object element KαThe output X-ray spectrum of energy is filtered, and adjusts the K for being only higher than at least one object elementαThe cathode electricity of energy Pressure.
Therefore, the transmission target X-ray tube of high dose output and application method are characterized in that it generates symmetrical X and penetrates The ability of the field of line.
The transmission target X-ray tube of high dose output and another feature of application method are that it provides biggish surface Ability of the product anode target to radiate.
The transmission target X-ray tube of high dose output and another feature again of application method are their ability to using difference Z material with using will increase radiant output characteristic X-ray ability.
The transmission target X-ray tube of high dose output and another feature again of application method are that it is lower using having The target material of fusing point is with the ability for special applications (such as generation of homogeneous X-ray) and treatment use.
The transmission target X-ray tube of high dose output and another feature again of application method are them using compared with low electrode Current potential is to generate the ability of higher output radiation.
The transmission target X-ray tube of high dose output and another feature again of application method are that its new anode of offer is matched The ability set, this allows to using the replaceable target material with different characteristic X-ray.
The transmission target X-ray tube of high dose output and another feature again of application method are that it provides X-ray tube Ability, which requires not radiated or limited heat dissipation in the form that air is cooling or liquid is cooling.Further, since The surface area of new anode arrangement increases, therefore compulsory air is cooling more effective.
High dose output transmission target X-ray tube and application method again another feature be its provide have due to The ability of high surface area anode target heat-sinking capability and the X-ray tube in increased service life.
The transmission target X-ray tube of high dose output and another feature again of application method are that it is provided for anode New construction and geometry are to increase the ability of the surface area of anode.
The transmission target X-ray tube of high dose output and another feature again of application method are that it is provided with more preferable The ability of the anode arrangement of heat-transfer character, this will enable anode operate at lower temperatures, and it is it is achieved that lower The radiant output of selection and the raising of melting material, and extend the service life of X-ray tube.
The transmission target X-ray tube of high dose output and another feature again of application method are that it is provided for cathode The ability of new construction and geometry, this makes electronics towards new construction and the deflection of the anode of geometry and/or accelerates.
The transmission target X-ray tube of high dose output and another feature again of application method are that it is provided for filament The ability of new construction and geometry, filament release equally distributed electronics towards new construction and the anode of geometry.
The transmission target X-ray tube of high dose output and another feature again of application method are them by minimum anode mesh Mark is supplied to the ability of radiation sample distance, to generate the x-ray source that can be placed closer to object.
The transmission target X-ray tube of high dose output and another feature again of application method are that it is generated for biology Or organic material radiation, radiotherapy, by killing or changing, human body cell treats certain diseases, the X-ray of imaging (such as is cured It treats, industry and double energy, to the non-destructive estimation of object, X-ray defect, X-ray diffraction mode, therapeutic X-ray, point Analyse X-ray and X-ray microscope) ability.
Another feature again of the transmission of high dose output and the target X-ray tube of reflection and application method is its generation The ability of the reflection photon that has dosage opposite with the traveling of the forward direction electronics of target anode.From the Z axis figure of X-ray field can from To the phenomenon.
Hemispherical and corresponding cathode construction due to anode, the transmission of high dose output and the target X of reflection are penetrated Another feature again of spool and application method is the energy that electron field is passively manipulated by changing the distance between two structures Power.
Another feature again of the transmission of high dose output and the target X-ray tube of reflection and application method is to change lamp Silk size and shape are to change the ability of electron emission characteristic.
For those skilled in the art, when being read with reference to the accompanying drawings, high dose output transmission and These and other feature of the target X-ray tube of reflection and application method will be to the following of exemplary embodiment and claim Detailed description becomes more apparent upon.
Detailed description of the invention
The detailed description to exemplary embodiment is read by reference to attached drawing, is better understood with the saturating of high dose output Transmission objectives X-ray tube and application method are penetrated, in the accompanying drawings, identical appended drawing reference always shows similar structure and refers to It is similar element, and in the accompanying drawings:
Fig. 1 is that the schematic cross-section of the prior art X-ray tube of Coolidge type indicates；
Fig. 2 is that the schematic cross-section of the exemplary embodiment of transmission target X-ray tube indicates, is shown just from yin The section for the electron trajectory line that pole filament is launched and show the section for the output radiation just launched from anode target；
Fig. 3 is the graphical representation of the relatively golden target dose of X-ray energy keV；
Fig. 3 .1 is the figure of X-ray energy keV such as tungsten, iridium relatively and gold as the combined dosage of the material of target It indicates；
Fig. 4 is the graphical representation of the target anode thickness dosage of difference kV relatively；
Fig. 5 is to be indicated using the transmission target X-ray tube of Fig. 2 come the diagram of the sample application of irradiating biological materials；
Fig. 6 be the exemplary embodiment that the transmission target X-ray tube of Fig. 2 is combined with monochromatic filter schematically just It is indicated depending on cross section；
Fig. 7 is the figure for the dosage that X-ray energy Relative Transmission transmission objectives X-ray tube is combined with the monochromatic filter of Fig. 6 Shape indicates；
Fig. 8 is that the schematic front cross section of the alternative exemplary embodiment of transmission target X-ray tube indicates, is shown Go out the section for the electron trajectory line just launched from cathode filament and shows the output spoke just launched from anode target The section penetrated；
Fig. 9 is the flow chart for generating the method for X-ray field of symmetric shape；
Figure 10 is the schematic cross-section table of the alternative exemplary embodiment of the target X-ray tube of transmission and reflection Show, show the section for the electron trajectory line just launched from cathode filament and show just launch from anode target and from The section for the output radiation that anode target reflects；
Figure 11 A is the cross section of the alternative exemplary embodiment of the transmission of Figure 10 and the target X-ray tube of reflection It indicates, shows with the pipe side wall extended；
Figure 11 B is the cross section of the alternative exemplary embodiment of the transmission of Figure 10 and the target X-ray tube of reflection It indicates, shows with the pipe side wall shortened；
Figure 12 is the cross section table of the alternative exemplary embodiment of the transmission of Figure 10 and the target X-ray tube of reflection Show and the graphical representation of photon relevant to tube hub line or the photon intensity of radiation；And
Figure 13 is using the transmission of Figure 10 and the target X-ray tube of reflection come the sample application of irradiating biological materials Diagram indicates.
It should be noted that the attached drawing presented is intended merely for the purpose of explanation, and therefore they be both not intended to or not It is intended to for the disclosure being limited to any or all fine detail of shown structure, in addition to that may be considered to claimed at them The most important range of invention in except.
Specific embodiment
When describing the exemplary embodiment of the disclosure, as shown in Fig. 1-3,3.1,4-10,11A, 11B, 12-13, it is For the sake of clear, specific term is used.However, the disclosure is not limited to the specific term so selected, and to manage Solution, each particular element includes being operated in a similar manner to complete all technically equivalent ones of similar functions.It illustrates herein Example be non-limited example, and the only example in other possible examples.
Referring now to Figure 1, the schematic cross-section of shown Coolidge type X-ray tube 12 indicates, as shown in Figure 1, packet Include: X-ray tube shell 1 can be glass or metal；High voltage insulator 2；And vacuum dielectric 3, it is comprised in X-ray Tube shell 1 is wherein.In Coolidge pipe, the x-ray photon of fan-shaped output radiation mode 7 is shown as by hitting from filament 5 The electron beam (being illustrated as electron trajectory 6) that is issued on the surface of target anode 9 (being illustrated as X-ray target 9) and generate. Coolidge pipe can be with single-ended operation, and wherein cathode (being illustrated as cathode assembly 4) is in negative potential and anode 9 is in ground connection, Or both-end operation, wherein cathode 4 is in negative potential and anode 9 is in positive potential.In any configuration, the energy of acceleration Amount is the difference between electrode potential.In Coolidge X-ray tube, target anode 9 is by such as heavy metal of tungsten, tantalum or iridium It is made, and due to their density (tungsten -19.35, tantalum -16.65 or iridium -22.4gr/cm3 (gram per cubic centimeter)) and Gao Rong Point (tungsten -3410, tantalum -2996 or -2410 degrees Celsius of iridium (C)) and select this material.The material of target anode 9 is most frequently pacified (it is illustrated as anode heat conductor 8) on the Heat Conduction Material of such as copper.In addition, being used in Coolidge type X-ray tube design 12 The amount of electric flux between the electrode potential for generating given gained radiation 7 be it is very high, result in 9 material of target anode Heating requirements specific objective it is cooling consider, such as rolling target anode 9, carry out that air is cooling or liquid is cold to target anode 9 But, such as by water or dielectric oil cooling line 10 is flowed through.Carrying out cooling purpose to anode assemblies is the higher of realization X-ray tube The operation of power.
The placement in addition, target anode 9 and electron beam 6 are in line, and obtained radiation 7 is by forming output radiation 7 Beam output radiation window 11 to be emitted with the angle at right angle of electron beam 6.
Referring now to Figure 2, by way of example, and not limitation, the transmission target X for showing high dose output is penetrated The schematic cross-section of the exemplary embodiment of spool 20 indicates.Preferably, transmission target X-ray tube 20 includes that evacuation is close Envelope room or encapsulation, such as shell 21 can be glass, alloy or metal, and which create rarefied spaces 25.Shell 21 One end, first end 21.1 are preferably connected to the first connector 31 of high voltage power supply 33.The main member being comprised in shell 21 Part is preferably anode construction 22, cathode construction 23, the first heater lead 27, the second heater lead 28 and filament 24.In addition, Anode construction 22 preferably includes the anode of the transmission target 43 as a part of anode construction 22, and wherein target 43 is excellent Selection of land is deposited on the inner surface 42 of the first end 21.1 of shell 21.Cathode construction 23 may be coupled to ground connection or high voltage power supply 33 The second connector 32.Filament 24 is preferably connected to the first heater lead 27 and heated current power supply of heated current power supply 44 44 the second heater lead 28.Preferably, target 43 is deposited on the electronics on the inner surface 42 of the first end 21.1 of shell 21 Interact material and electric arc (arcing) or circular cross section, dome or hemispheric first end together with shell 21 21.1 include anode construction 22.The preferably high voltage insulator 26 being also contained in shell 21, partly closes shell 21, in the second end 21.2 of shell 21.
Bremsstrahlung and characteristic radiation 30 preferably with electric arc or semi-circular cross-section, dome or hemispherical radiation mode from Emit in transmission target X-ray tube 20.It is produced when high energy electron is issued from heat filament 24 and is accelerated by high voltage power supply 33 Give birth to characteristic radiation, the anode construction 22 on the surface of target anode structure 22 and the electric energy between the electrode potential of cathode construction 23 Electronics is hit its track from object element (target 43) by (being illustrated as electron trajectory 35).When it happens, next higher energy Electronics in amount track will fall into the lower energy levels, and the radiation for issuing energy difference between equal to two electron orbits is quick-fried Hair.Because each element or material of target 43 have different atomic structures, the energy level for the radiation launched is The unique and feature of the element.Atomic level be designated as K, L, M, N...... and it is each it is horizontal have be appointed as α, The other son of β ... is horizontal.For example, if there are vacancy (vacancy) and electronics in the K track of element (target 43) Decline from L track to fill vacancy, then the energy issued is equal to EX-ray=Ekα-EL.Main and the most useful characteristic radiation is The K of various elements (target 43)αEnergy level, and the electric energy between anode construction 22 and the electrode potential of cathode construction 23 Energy be less than high voltage power supply 33 100 kilovolts of (kV) Shi Fasheng.Herein it is appreciated that transmission target X-ray tube 20 The K of target 43 or the complex target 43 being made of various elements preferably can be usedαCharacteristic radiation is filled lower than 100 kilovolts (kV) X-ray spectrum and the X-ray tube that excellent performance characteristic is generated using the bremsstrahlung from higher Z element.
43 material of Table I target or combined material
Anode material (43) Bremsstrahlung Characteristic radiation Global radiation
Tungsten 700 300 1000
Tungsten+gold 700 600 1300
Tungsten+gold+iridium 700 900 1600
For all readings of tungsten anode being standardized and the operation at 200kV.
A kind of new shell and target anode planform
In order to solve the disadvantage that Conventional X-ray tubes and electric current transmission pipe, there is the transmission of selective anode construction 22 Transmission objectives X-ray tube 20 has been designed.Preferably, transmission target X-ray tube 20 is various to that can deposit thereon 43 element of target or material with formed anode construction 22 substrate (be electroplated using evaporation or sputtering technology via electrochemistry plate, Mechanical bond or vapor deposition in one on anode construction formed an object element) using by high Z materials (such as aluminium or Beryllium, carbon, ceramics, stainless steel or its alloy) formed the major diameter 52 of anode construction 22 of shell 21, hemispherical dome structure.It is preferred that Ground uses hemispherical anode construction 22, this is because it has twice of surface area of the discoid substrate of same diameter.Hemisphere face Product is 2 π r2, and disc area is π r2.This increase of surface area allows to increase power dissipation, and the electronics improved in target 43 is symmetrical Property, increase surface area to radiate, and therefore improve cooling efficiency.In addition, anode grid substrate 22 can be coated with as target 43 Various elements, the combination of element or their alloy generate desired feature form anode construction 22 and to be specific purpose Radiate 30 or coated with high Z element to generate increased output using bremsstrahlung and the combination of characteristic radiation 30.With Coolidge type X-ray tube is compared, and for identical 30 output of radiation, this is all in reduced cathode potential, high voltage power supply 33 Place completes, as shown in Figure 1.
Herein it is appreciated that the hemispherical anode construction 22 configured with high surface area is dissipated on large surface area due to it The ability of heat and cause from cooling or relatively cooling or lower temperature anode, and therefore do not require any inner cooling system (example Such as rotary anode or with the cooling fluid of inner passage), with the heat generated in the anode construction 22 that dissipates during operation.
Herein it is also recognized that the hemispherical anode construction 22 configured with high surface area is symmetrically provided across anode construction 22 electronics is uniformly distributed, and therefore generates being uniformly distributed for radiation 30.
The target anode substrate of specific coating
Preferably, transmission target X-ray tube 20 is using gold as the target for being coated hemispherical anode construction 22 43, it is deposited on the inner surface 42 of the first end 21.1 of shell 21 to form anode construction 22.Mesh as anode construction 22 The fitting for marking 43 elements has K at about 68.8keVαK at peak value and about 77keVβPeak value, when at 150 to 160 kilovolts (kV) when being operated, high voltage power supply 33, bremsstrahlung and characteristic radiation spectrum, radiation 30 as shown in Figure 3, are ideally fitted In one or more high output radiation applications and far superior to traditional X-ray tube, such as Coolidge type X shown in Fig. 1 Ray tube, this is because following advantages.Preferably, 43 element of golden target of anode construction 22 provides the advantage that, this be because Generation efficiency for radiation 30 is directly proportional to the atomic number of golden target 43 of anode construction 22 of the kV multiplied by high voltage power supply 33. Here, for Coolidge type X-ray tube, the atomic number of golden (Au) is 79, and the atomic number of tungsten (W) is 74, as shown in figure 1 institute Show.Percentage difference between two atomic numbers is 6.75%.Based on formula 1- ((kV*z)/(kV* for calculating radiation 30 Z)) * 100=efficiency kV*Z*10-6；Gold as target anode structure 22 is 6.75%, be directed to Coolidge type X-ray It is more efficient when generating bremsstrahlung, radiation 30 under tungsten (W) target 43 identical kilovolt (kV) of pipe is horizontal, institute as shown in figure 1 Show.Traditional X-ray tube cannot be golden as 43 material of target for being directed to high power irradiation tube using using, this is because due to The gold (1064 degrees Celsius) compared with tungsten (3422 degrees Celsius) of the small surface area design of the anode 8 of Coolidge type X-ray tube Fusion temperature it is lower, shown in Fig. 1.However, the hemisphere of the anode construction 22 for transmission transmission objectives X-ray tube 20 Larger 43 area of target provided by shape structure, anode surface area 22 increases, to allow increased power dissipation；And therefore, Element (such as gold) compared with low melting point can be used for target 43.For example, compared with 1 square inch of the anode 9 of Fig. 1, anode knot The area of structure 22 can be greatly to 25 square inches, can be in 1,000,000 W/cm2Under operated.It is contemplated herein that be for target 43 it is other compared with low melting point element (such as element of the atomic number between 74 to 82, and more particularly, lead (Pb) and uranium (U) etc.) it may be used as 43 material of target for being directed to anode construction 22.It is also contemplated herein, for the target of anode construction 22 The preferred 4-40 micron thickness of 43 materials, and depend on for target 43 select material, required type radiation 30 transmitting with And high voltage power supply 33 acceleration voltage and the thickness of 43 material of selection target.These characteristics enable homogeneous beam in high voltage power supply There is increased radiation under 33 lower kV.
Target 43 is preferably by suitable material (such as golden (Au) or lead (Pb), including with the atom between 74 to 82 Other elements of ordinal number) it is formed, and in addition copper (Cu), silver-colored (Ag) and uranium (U) can be used for target anode structure 22.It is preferred that Ground, these materials include other suitable characteristics, such as high KαEnergy level, the high-conversion rate of electronics to X-ray or this field Other beneficial characteristics that technical staff understands.
In addition, the filament 24 of transmission target X-ray tube 20 is preferably configured as electric arc or circular cross section or half Spherical arrangement is located in cathode construction 23 wherein, and this configuration makes electron beam 29 along electron trajectory 35 towards anode construction 22 carry out electrostatic focusing, or more particularly, with the 180 degree (180 °) or the progress of hemispherical mode in the target 43 of anode construction 22 Electrostatic focusing, make electron beam 29 be evenly distributed in target 43, shell 21 anode construction 22 first end 21.1 inner surface On 42.In addition, filament 24 is preferably coated with about 40-50 microns of thick oxide material, and use is connected to heating electricity The nicon conducting wire of second heater lead 28 of first heater lead 27 and heated current power supply 44 in galvanic electricity source 44 carrys out indirect heating Carry out heat filament 24, is used to discharge electronics from filament 24 to provide thermal vibration energy.As described above, across target 43 and anode knot This distribution of the electron beam 29 of structure 22 reduces or reduces watt density (watt/area, the W/ of target 43 and anode construction 22 cm2) load, and therefore prevent the hot spot due to caused by being evenly heated of target 43 and anode construction 22.
Herein it is appreciated that the offer symmetrical in combination of hemispherical anode construction 22 and electric arc or hemispherical filament 24 is across mesh The equiblibrium mass distribution of the electronics of mark 43 and anode construction 22.
Herein it is also recognized that hemispherical anode construction 22 and electric arc or hemispherical filament 24 are provided in combination across target 43 and anode construction 22 collimation electron trajectory 35.
Herein it is also recognized that hemispherical anode construction 22 and electric arc or the combination of hemispherical filament 24 provide balanced electricity Sub- travel distance 58, electron beam 29 advance to the distance of target anode structure 22 from filament 24.
Again in addition, the cathode construction 23 of transmission target X-ray tube 20 be preferably configured as ' V' shape or notch ' V' Shape cross section bowl-shape or horn-like (flared) configuration etc., and this configuration statically guides electron beam 29 (effectively and Weighing apparatus ground is distributed to target 43 towards target 43 and anode construction 22 or more particularly with 180 degree (180 °) mode along electron trajectory 35 On anode construction 22) so that electron beam 29 is evenly distributed in the first of half-spherical object 43 and anode construction 22, shell 21 On the inner surface 42 at end 21.1.
Herein it is appreciated that hemispherical anode construction 22, electric arc or hemispherical filament 24 and horn-like cathode construction 23 The maximum of the directionality X-ray about center line CL near symmetrical is provided in combination to generate.
Herein it is appreciated that transmission-type target X-ray tube 20, which may include, has the anode knot of specific coating target 43 Structure, such as the parameter by using 43 material of target.
Herein it is appreciated that transmission target X-ray tube 20 may include the anode construction 22 for X-ray deflection Specific coating target 43, such as by using the high Z materials for target 43.
Herein it is appreciated that transmission target X-ray tube 20 may include the anode construction 22 for X-ray deflection Specific coating target 43, such as by using the low Z materials for target 43.
Herein it is appreciated that being directed to the low power requirements of high voltage power supply 33 or being applied for high dose radiation 30, thoroughly The specific coating target 43 that transmission objectives X-ray tube 20 may include anode construction 22 is penetrated, such as by using 43 material of target Parameter.
Herein it is appreciated that transmission target X-ray tube 20 may include the anode construction 22 for medical imaging Specific coating target 43, such as by using molybdenum as 43 material of target.
Herein it is appreciated that transmission target X-ray tube 20 may include the anode construction 22 for industry imaging Specific coating target 43, such as increase as 43 material of target by using gold the quantity of x-ray photon, then improve Picture contrast.
Referring now to Figure 3, by way of example, and not limitation, showing the X for transmission target X-ray tube 20 Ray energy keV (λ) is shown with respect to the graphical representation of output radiation dosage with 43 gold medal material of target.In 43 gold medal material of target In the figure of the characteristic radiation R1 of material, Y-axis indicates the dosage (as unit of photon) of the output radiation (radiation 30) of specified rate, example Such as photon numbers, and X-axis indicates the kilovolt (wavelength) of the X-ray energy of specified rate, and with the variation of kilovolt (wavelength), by Also change for the quantity for the photon doses that the figure of gold indicates.As shown in the figure, there is radiation spike and be assigned therein as Kα And KβDosage peak value is characteristic radiation peak value caused by as using 43 gold medal material of target.Lead to mesh using 43 gold medal material of target The dose of radiation for marking 43 materials increases, and increases input power kV (λ) without requiring, this is because radiation spike is shown as about Corresponding to KαThe 68.7kV (λ) of peak value and correspond to KβThe 77kV (λ) of peak value.
Referring now in Fig. 3 .1, by way of example, and not limitation, show for transmission target X-ray tube 20 X-ray energy kV (λ) shows the combination with the material based on target 43 with respect to the graphical representation of output radiation dosage And 43 material of target configured.Preferably, target 43 is preferably by suitable material (such as gold (Au), lead (Pb), including have The other elements and other copper (Cu) of atomic number between 74 to 82, silver-colored (Ag) and uranium (U)) it is formed.In golden tungsten and iridium Composite object 43 characteristic radiation R2 the figure in, Y-axis indicate specified rate radiation dosage (as unit of photon), such as The quantity of photon, and X-axis indicates the kilovolt (wavelength) of the X-ray energy of specified rate, and with the variation of kilovolt (wavelength), Photon doses quantity can also change.As shown in the figure, there is the K for both radiating spike and being assigned therein as golden tungsten and iridiumα And KβPeak value is characteristic radiation peak value caused by as using the combination of materials of target 43.Use 43 material of target of golden tungsten and iridium Output radiation (radiation 30) dosage that material causes combined material, target 43 to occur increases, and increases input power kV (λ) without requiring High voltage power supply 33, as shown in Table II.
Table II
Element Kα1 Kα2 Kβ1 Kβ2
Gold 68.804 66.990 77.985 80.182
Tungsten 59.318 57.982 67.244 69.1
Iridium 64.896 63.287 73.560 75.620
Herein it is appreciated that constituting combined material, needle for the every kind of material selected from element list above To target 43, as shown, the characteristic radiation R2 of target 43 will be with additional and different KαAnd Kβ, selected and added To the peak value of every kind of material of target 43.Herein it is also recognized that the addition of the every kind of material selected from list above is led 43 material of target based on multiple material and every kind of material is caused to generate additional and different KαAnd Kβ, peak value, and therefore increase defeated Dose of radiation out increases input power kV (λ), high-voltage electricity without requiring for the radiation 30 that the target 43 of combined material occurs Source 33, as shown in the area increase of the curve graph as characteristic radiation R2.By adding multiple combinations listed above for target 43 Material, the improvement output radiation occurred for the target 43 of combined material (radiation 30) dosage will greatly increase.If 1000 watts Power generate 100 gray(Gy)s (Gray) dosage, then the dosage more than 50% can be generated in composite object 43.
Also again it is appreciated that based on list of materials above, for output radiation (radiation 30) agent of 43 material of target The increase of amount increases input power (kV (λ) * mA) without requiring, requires it reduce cooling.
Also again it is appreciated that based on list of materials above, for output radiation (radiation 30) agent of 43 material of target The increase of amount increases input power (kV (λ) * mA), high voltage power supply 33 without requiring, this can be realized compared with low input power The radiation and irradiation application of (kV (λ) * mA), such as medical applications.
Referring now to Figure 4, by way of example, and not limitation, showing for transmission target X-ray tube 20 The graphical representation with empirically determined thickness relative dosage output radiation (radiation 30) of 43 material of target.It is caused in a piece of wood serving as a brake to halt a carriage of target 43 In the figure for radiating relative material thickness, Y-axis indicates the dosage (as unit of photon) of the output radiation (radiation 30) of specified rate, Such as number of photons, and X-axis indicates 43 material thickness of target (as unit of micron), and with 43 material thickness variation of target, Also changed by the number of photons of graphical representation.For the high voltage power supply 33 of variation, representative curve shows 22 He of anode construction Electric energy between the electrode potential of cathode construction 23, such as 50kV Ra, 100kV Rb and 200kV Rc.In each curve, Dosage is based on increased 43 material thickness of target and ramps up, steadily (plateaus) and is gradually reduced.In Fig. 4 herein It is appreciated that the thickness of 43 material of target of target anode structure 22 is preferably about 4-40 microns, and target anode knot The thickness of 43 material of target of structure 22 is more preferably about 4-18 micron, and depending on selected material, required type The thickness of the acceleration voltage of 30 transmitting of radiation and high voltage power supply 33 and 43 material of selection target.
In Fig. 4, herein it is also recognized that higher acceleration voltage, high voltage power supply 33, more efficient transmission mesh Mark X-ray tube 20, which is in, is converted into increased dosage output radiation 30 for the electronics emitted by filament 24, to utilize characteristic radiation Peak value.
In Fig. 4, herein it is also recognized that in characteristic radiation R-curve 50kV Ra, 100kV Rb and 200kV Rc There is not cusp, and more particularly, representativeness radiation R-curve 50kV Ra has from the about 3-5 micron thickness of target 43 Steadily, representative radiation R-curve 100kV Rb has steady, the representative radiation R from the about 7-10 micron thickness of target 43 bent Line 200kV Rc has from the steady of the about 14-18 micron thickness of target 43 and common representative radiation R-curve 50kV Ra, 100kV Rb and 200kV Rc have from the steady of the preferred 4-18 micron thickness of target 43.
Transmission target X-ray tube 20 design variable (such as will for target 43 select material (have from 73 to 79 The material of the Z of a heavy element), 43 material thickness of selected target (as unit of micron) and selected high voltage power supply 33 voltage) dosage output radiation 30 is changed, such as with the increase dosage output radiation of lower 33 power of high voltage power supply.
In Fig. 4, herein still again it is appreciated that 43 material of selected 43 material of target and/or selected target The change for expecting thickness (as unit of micron), changes dosage output radiation 30.
In Fig. 4, still operated under two voltages of such as 50kV and 100kV it is appreciated that having again herein The transmission target X-ray tube 20 with high voltage power supply 33 double energy can be preferably chosen target 43 material it is thick Degree is to adapt to two kinds of energy, for example, can choose 43 material thickness of target between 3-10 microns, wherein having from target 43 The stable representativeness of the about 3-5 micron thickness of (50kV) radiates R-curve 50kV Ra and has the pact from target 43 (100kV) The stable representative radiation R-curve 100kV Rb overlapping of 7-10 micron thickness.
Referring now to Figure 5, by way of example, and not limitation, show using transmission target X-ray tube 20 come The sample application of irradiating biological materials, it is as shown in Figure 2 and described.When in use, the spy of transmission target X-ray tube 20 Sign radiation and bremsstrahlung 30 are preferably from transmission target X-ray tube 20 with electric arc or semi-circular cross-section, dome or half Spherical shape 30 Mode Launch of radiation.Preferably, transmission target X-ray tube 20 generates characteristic radiation 30, and this feature radiates 30 quilts It is configured so that the intense radiation 30 of large area can improve handling capacity and radiate and radiate more or increased number of sample S simultaneously. In addition, sample S can be positioned proximate to or the anode construction 22 of the shell 21 of neighbouring transmission target X-ray tube 20, or Person is positioned static or passes through mechanically moving structure positioning, this, which is determined by using the geometry of radiation mode, increases The application of the uniform exposure level of sample S by characteristic radiation 30.In addition, transmission target X-ray tube 20 preferably exists 21.1 surrounding of first end of transmission target X-ray tube 20 generates symmetrical radiation field (radiation 30), with owning to sample S Region provides the radiation 30 of consistent dosage.
Herein it is appreciated that the output of radiation 30 and the Coolidge type prior art of transmission target X-ray tube 20 X-ray tube be in comparison it is increased, shown in Fig. 1.For example, if transmission target X-ray tube 20 exports twice of spoke 30 are penetrated, then the half of runing time needed for sample S requirement transmission target X-ray tube 20, and in addition use to height The higher dosage that the lower-wattage of voltage source 33 requires radiates in the 30, BTU with the saving of lower electricity needs air conditioner load Relatively low heat loads, high voltage power supply 33, all relatively lower operational costs for all having caused transmission target X-ray tube 20.In addition, The hemispherical anode construction 22 for being configured with high surface area is caused cooling or colder or lower temperature due to its heat-sinking capability Anode, and any internal or external cooling system, such as rotary anode or the cooling fluid with inner passage are not therefore required, With the heat generated in anode construction 22 during operation that dissipates, and therefore reduce transmission target X-ray tube 20 Operating cost.
Referring now to Figure 6, by way of example, and not limitation, it is (replaceable to show transmission target X-ray tube 20 Ground 50) schematic cross-section of combined with monochromatic filter 60 high dose output indicates.Preferably, monochromatic filter 60 can be with Be positioned proximate to or the first end 21.1 of the shell 21 in the path of neighbouring radiation 30 or shell 21 anode construction 22 with Between sample S in the path of radiation 30, so as to filter from the selected attenuation for radiating 30 or to it.Referring again to FIGS. 3, By way of example, and not limitation, monochromatic filter 60, which can be configured as, is filtered specified radiation 30 or it is made to decline Subtract, is, for example, less than all radiation of 54kV (λ), to generate KαAnd KβThe specified radiation 30 of dosage peak value is using 43 gold medal of target Characteristic radiation peak value caused by material.
Fig. 7 is the dosage that X-ray energy Relative Transmission transmission objectives X-ray tube 20 is combined with the monochromatic filter of Fig. 6 Graphical representation.In the figure of the characteristic radiation R1 of 43 gold medal material of target, Y-axis indicates the dosage of the output radiation 30 of specified rate (as unit of photon), such as number of photons, and X-axis is represented to the kilovolt (wavelength) of quantitative x-ray energy, in 75kV (λ) and Between 85kV (λ), and as kilovolt (wavelength) changes, also changed by the photon numbers indicated for the dose 30 of gold. As shown in the figure, there is radiation spike and be assigned therein as KαAnd KβDosage peak value is led by using 43 gold medal material of target The characteristic radiation peak value of cause.When in use, selected 43 material of target and its KαAnd KβDosage peak value and selected monochrome Filter 60 preferably implements the expectation radiation profiles of radiation 30, and therefore can be designated as being directed to transmission target X Ray tube 20 (alternatively 50) realizes that various specific radiations 30 are distributed, for specified image and treatment example or use On the way.
Referring now to Figure 8, by way of example, and not limitation, showing the high agent of transmission target X-ray tube 50 The schematic cross-section for measuring the alternative exemplary embodiment of output indicates.Preferably, transmission target X-ray tube 50 includes Room or the encapsulation of sealing, such as shell 21 are evacuated, can be glass, alloy or metal.One end of shell 21, first end 21.1 It is preferably connected to the first connector 31 of high voltage power supply 33.The main element for including in shell 21 is preferably anode construction 22, cathode construction 23.1, the first heater lead 27, the second heater lead 28 and filament 24.1.In addition, anode construction 22 is excellent Selection of land includes a part of the anode of transmission target 43 as anode construction 22, and wherein target 43 is preferably deposited shell The inner surface 42 of 21 first end 21.1 is thereon.Cathode construction 23.1 may be coupled to the second connection of ground connection or high voltage power supply 33 Device 32.Filament 24.1 be preferably connected to heated current power supply 44 the first heater lead 27 and heated current power supply 44 second Heater lead 28.Target 43 be deposited on the inner surface 42 of the first end 21.1 of shell 21 electron interaction material (that is, It is electroplated using evaporation or sputtering technology via electrochemistry plate, a shape on anode construction in mechanical bond or vapor deposition At an object element) and with the electric arc of shell 21 or circular cross section, dome or hemispheric first end 21.1, together Including anode construction 22.It still also include the preferably high voltage insulator 26 in shell 21, in the second end of shell 21 Shell 21 is partly closed on 21.2.
The filament 24.1 of transmission target X-ray tube 50 is preferably configured as straight line or summary in cathode construction 23.1 The cross section of microbend or the configuration of plane or dish type, and this configuration makes electron beam 29.1 along electron trajectory 35.1 towards target 43 and anode construction 22 carry out electrostatic focusing, or more particularly, with the focus point configuration mode in target 43 and anode construction 22 Carry out electrostatic focusing so that close to center line CL electron beam 29.1 concentrate on shell 21 first end 21.1 inner surface 42 On.
Again in addition, the cathode construction 23.1 of transmission target X-ray tube 50 be preferably configured as ' U' shape cross section, Or cylindrical configuration or other focusing configuration, and this configuration makes electron beam 29.1 along electronics narrow gauge mark 35.1 towards target 43 Accelerate with 22 electrostatic of anode construction, or more particularly, is accelerated in target 43 and anode construction 22 with focusing mode electrostatic, so that Electron beam 29.1 straitly divides on the inner surface 42 of the first end 21.1 of half-spherical object 43 and anode construction 22, shell 21 Cloth.This concentration of electron beam 29.1 can realize high dose output in the configuration of the narrow luminous point with anode diameter 52, and Transmission target X-ray tube 50 can be used for such as applying, to generate for radiotherapy, imaging (such as medical treatment, work The non-destructive estimation of industry and double energy, object) focusing X-ray.
As shown in Figure 2, it is contemplated that, spot diameter 52 can based on design factor (such as opening or gap, such as yin The internal diameter 56 of pole structure 23.1, electron beam 29.1 electronic journey distance 58 (electronics advances to target 43 and sun from filament 24.1 The distance of pole structure 22), and/or shell 21 hemispherical anode construction 22 diameter 52) and scale up/reduce or increase Big or reduction size.For example, when in use, the internal diameter 56 of cathode construction 23.1, electron beam 29.1 electronics from 24.1 row of filament Enter the diameter 52 of the electron travel distance 58 of target 43 and anode construction 22, and/or the hemispherical anode construction 22 of shell 21 It can be designated as realizing the spot diameter 52 proportional to the tumor size of radiotherapy depth that X-ray penetrates is subjected to.
Herein it is appreciated that hemispherical anode construction 22, filament 24.1 and the cathode construction 23.1 to narrow mention in combination For focusing, radial linear symmetrical X-ray field.
Herein it is appreciated that hemispherical anode construction 22, filament 24.1 and horn-like cathode construction 23.1 are given birth in combination At the orientation X-ray close to center line CL, with the therapeutic roentgenotherapia for melanoma and other cancer cells.
It is contemplated herein that be monochromatic filter 60 can be similar to Fig. 6 and 7 shown in and disclosed transmission mesh Mark X-ray tube 50 is used together.
Referring now to Figure 9, by way of example, and not limitation, showing the method for generating symmetrical hemispherical X-ray field Flow chart 900.In box or step 910, the transmission target X-ray tube 20/50 of high dose output, tool are provided Have and evacuates seal casinghousing 21, hemispherical anode construction 22, cathode construction 23, target 43 and filament 24 as described herein.? In box or step 915, the combination of material or material, z material is selected for target 43.In box or step 920, for height Voltage source 33 selects acceleration voltage.In box or step 925, cause the transmission target X-ray tube 20 of high dose output Generate the X-ray for biomaterial radiation.In box or step 930, the transmission target X for causing high dose to export is penetrated Spool 20 generates the X-ray of the non-destructive estimation for object.In box or step 935, high dose is caused to export saturating Transmission objectives X-ray tube 20 is penetrated to generate for the destructive X-ray treated to biological sample.Other treatments include imaging, example Such as medicine, industry and double energy, to the non-destructive estimation of object.
Referring now to Figure 10, by way of example, and not limitation, showing transmission and the reflection of high dose output The schematic cross-section of the alternative exemplary embodiment of target X-ray tube 50 indicates.Preferably, transmission and reflectance target X-ray tube 50 includes evacuating room or the encapsulation of sealing, such as shell 21, can be glass, alloy or metal.The one of shell 21 End, first end 21.1 are preferably connected to the first connector 31 of high voltage power supply 33.The main element for including in shell 21 is preferred Ground is anode construction 22, cathode construction 23.1, the first heater lead 27, the second heater lead 28 and filament 24.1.In addition, positive Pole structure 22 preferably includes a part of the anode of transmission and reflectance target 43 as anode construction 22, wherein target 43 It is preferably deposited on the inner surface 42 of the first end 21.1 of shell 21.Cathode construction 23.1 may be coupled to ground connection or high-voltage electricity Second connector 32 in source 33.Filament 24.1 is preferably connected to the first heater lead 27 and heating electricity of heated current power supply 44 Second heater lead 28 in galvanic electricity source 44.Target 43 is deposited on the electronics phase on the inner surface 42 of the first end 21.1 of shell 21 Interaction material and with the electric arc of shell 21 or circular cross section 2-D is circular or substrate or hemispheric first end 21.1 It together include anode construction 22.It still also include the preferably high voltage insulator 26 in shell 21, the second of shell 21 Shell 21 is partly closed on end 21.2.
Transmission and the filament of reflectance target X-ray tube 50 24.1 are preferably configured as straight in cathode construction 23.1 Line or slight curving cross section or the configuration of plane or dish type, and this configuration makes electron beam 29.1 along 35.1 court of electron trajectory To 22 Electrostatic deformation of target 43 and anode construction, or more particularly, with the large area electron mould in target 43 and anode construction 22 Formula Electrostatic deformation so that close to center line CL electron beam 29.1 be evenly distributed in shell 21 first end 21.1 inner surface On 42.In addition, filament 24.1 and cathode construction 23.1 can be positioned proximate to the electric arc of shell 21 or the 2-D of circular cross section The center line CL of round or substrate or hemispheric first end 21.1 be (circle created by the 2D substrate of hemispherical first end 21.1 Center) and between cathode construction 23.1.
Again in addition, transmission and the cathode construction of reflectance target X-ray tube 50 23.1 preferably or can be configured as ' U' shape cross section or cylindrical configuration or it is other defocus configuration, and this configuration makes electron beam 29.1 along electron trajectory 35.1 accelerate towards target 43 and 22 electrostatic of anode construction, or more particularly, accelerate to target 43 with defocus mode electrostatic On anode construction 22, so that first end 21.1 of the electron beam 29.1 in half-spherical object 43 and anode construction 22, shell 21 It is evenly distributed on inner surface 42.This distribution of electron beam 29.1 is realized (to be determined forward by photon direction 52 forward Justice is the same direction that the electronics of electron beam 29.1 is advanced with fan pattern from anode construction 22) and using opposite with anode 22 Reflecting photon direction 52.1, (reflection is defined as the electronics of electron beam 29.1 and is advanced with reflecting fan pattern from anode construction 22 Opposite direction) high dose output.When in use, the transmission of high dose output and reflectance target X-ray tube 50 are replaced Changing exemplary embodiment can be used for irradiating the batch of sample S via transmission and transmission and reflection target X-ray tube 50, such as thoroughly The symmetric radiation field (radiation 30) penetrated around the first end 21.1 of transmission objectives X-ray tube 50 is with to being positioned proximate to shell 21 The all areas of sample S of first end 21.1 radiation 30 of consistent dosage is provided, as shown in Figure 5；And transmission target X Replaceable radiation field (radiation 30) around the second end 21.2 of ray tube 50 is to be parallel to center line CL and connect to being positioned in The all areas of the sample S of nearly shell 21 (and more particularly, close to the second end 21.2 of shell 21) provide consistent dosage Radiation 30, as shown in figure 13.
Referring now to Figure 11 A, by way of example, and not limitation, transmission and the reflection of high dose output are shown The cross section of the alternative exemplary embodiment of target X-ray tube 50A indicates, shows the anode of reduction to cathode spacing.It is excellent Selection of land, the transmission of high dose output and the alternative exemplary embodiment of reflectance target X-ray tube 50A can be configured as First end 21.1 with shell 21 is positioned in and anode of the second end 21.2 of shell 21 at linear distance 110A Structure 22 or cathode construction 23.1；Wherein electron beam 29.1 is realized (to be defined as forward by photon direction 52A forward The same direction that the electronics of electron beam 29.1 is advanced with wide fan pattern from anode construction 22) and using opposite with anode 22 anti- Penetrating photon direction 52.1A, (reflection is defined as the electronics of electron beam 29.1 to reflect wide fan pattern from anode construction 22 and advance Opposite direction) high dose output.
Referring now to Figure 11 B, by way of example, and not limitation, transmission and the reflection of high dose output are shown The cross section of the alternative exemplary embodiment of target X-ray tube 50B indicates, shows increased anode to cathode spacing.It is excellent Selection of land, the transmission of high dose output and the alternative exemplary embodiment of reflectance target X-ray tube 50B can be configured as First end 21.1 with shell 21, or it is positioned in the anode with the second end 21.2 of shell 21 at linear distance 110B Structure 22 or cathode construction 23.1；Wherein electron beam 29.1 is realized (to be defined as electricity forward by photon direction 52B forward The same direction that the electronics of beamlet 29.1 is advanced with narrow fan pattern from anode construction 22) and the use reflection opposite with anode 22 (reflection is defined as the electronics of electron beam 29.1 and is advanced with reflecting narrow fan pattern from anode construction 22 photon direction 52.1B Opposite direction) high dose output.
As shown in Figure 2, it is contemplated that, spot diameter 52 can based on design factor (such as opening or gap, such as yin The cathode internal diameter 56 of pole structure 23.1, electron beam 29.1 electronic journey distance 58 (electronics from filament 24.1 advance to target 43, The distance of anode construction 22), and/or shell 21 hemispherical anode construction 22 diameter 52) and scale up/reduce or Increase or reduce the size of radiation 30.
Referring now to Figure 11 A, 11B and 12, by way of example, and not limitation, show across (such as the light of radiation 30 Sub- P (transmission X-ray field or spectrum)) and reflected radiation 30 (such as reflection photon Pr (transmission and reflection X-ray field or light Spectrum)) photon intensity about transmission target X-ray tube 50 tube hub line C1 graphical representation.In the mark of the radiation 30 In the figure of standardization quantity, such as transmission is opposite away from the second of shell 21 with the photon P/Pr of transmission and reflection target X-ray tube 50 Hold the distance in millimeters of the baseline insulator 26 of 21.2 top enfeoffment closed shell bodies 21.In addition, referring again to Figure 12, Y Axis indicates the specified rate of the tube hub line C1 about transmission and reflectance target X-ray tube 50 or output radiation (radiation 30) The standardization number of photons P/Pr (as unit of photon) of photon P and reflection photon Pr, such as photon numbers, and X-axis indicate away from The distance in millimeters of the baseline insulator 26 of the 21.2 top enfeoffment closed shell body 21 of second end of shell 21.Figure 12's In the exemplary diagram, the first end 21.1 or anode construction 22 of shell 21 are positioned in second end 21.2 or cathode away from shell 21 The linear distance 110A of structure 23.1 can be about 275 millimeters (275 millimeters), and standardization number of photons P/Pr base It is ramped up in linear distance 110A, is steady and be gradually reduced.Herein it is appreciated that standardization number of photons in Figure 12 P/Pr is ramped up at about 75 millimeters (75 millimeters), from about 75 millimeters (75 millimeters) to about 250 It is steady at millimeter (250 millimeters), and be gradually reduced at hereafter 250 millimeters (250 millimeters).
It is contemplated herein that design considerations listed above can be used for being altered or modified by transmission and reflectance target Positioning, position, amount and the quantity for passing through photon P and/or reflecting photon Pr that X-ray tube 50 generates.
As shown in Figure 11 A, 11B and 12, it is contemplated that, design factor, this linear range 110 (such as determined First end 21.1 or anode of the position in the shell 21 of the linear distance 110 of second end 21.2 or cathode construction 23.1 away from shell 21 Structure 22) and it is this adjustment, design or predetermined linear range 110 change the target X-ray tube 50 by transmission and reflection The quantity of the reflection photon Pr (transmission and reflection X-ray field) of generation and position.
In Figure 12, herein it is also recognized that spot diameter 52 can based on design factor (for example, as shown in Figure 2, The linear range of the first end 21.1 or anode construction 22 of shell 21 and second end 21.2 or cathode construction 23.1 away from shell 110A and opening or gap, such as the electronic journey distance 58 of the cathode interior diameter 56 of cathode construction 23.1, electron beam 29.1 The hemispherical anode construction 22 of (distance that electronics advances to target 43, anode construction 22 from filament 24.1), and/or shell 21 Diameter 52) and scale up/reduce or increase or reduce the size for reflecting photon Pr or side output radiation 30.
Referring now to Figure 13, by way of example, and not limitation, show using transmission target X-ray tube 50 come The sample application of irradiating biological materials, it is as shown in Figure 10 and described.When in use, transmission target X-ray tube 50 is special Sign radiation and bremsstrahlung 30, P preferably from transmission target X-ray tube 50 with electric arc or semi-circular cross-section, dome or 30 mode of hemispherical radiation (symmetrical hemispherical transmission and reflection X-ray field) and reflected radiation 30 emit, and Pr is preferably from shell 21 anode construction 22 reflects, as shown in Figure 12.Preferably, transmission and transmission and reflection target X-ray tube 50 generate feature spoke Penetrate 30, this feature radiation 30 is configured such that the intense radiation 30 of large area can improve handling capacity radiation and reflected radiation and same When radiate more or increased number of sample S.In addition, sample S can be positioned proximate to, near or adjacent to transmission target The anode construction 22 of the shell 21 of X-ray tube 50 is either positioned static or passes through mechanically moving structure positioning, this is depended on Increase the sample by characteristic radiation 30 (pass through photon P and/or reflect photon Pr) by the geometry using radiation mode The application of the uniform exposure level of this S, as shown in Figure 12.In addition, transmission target X-ray tube 50 is preferably passed in transmission The first end 21.1 and 21.2 surrounding of second end of the shell 21 of defeated target X-ray tube 50 generate symmetrical radiation field (radiation 30) (passing through photon P and/or reflection photon Pr), to provide the radiation 30 of consistent dosage to all areas of sample S.
Herein it is appreciated that by and transmission and reflection target X-ray tube 50 radiation 30 output with Coolidge type show The X-ray tube of technology be in comparison it is increased, as shown in fig. 1.For example, if transmission target X-ray tube 50 is defeated Twice of radiation 30 out, then the half of runing time needed for sample S requirement transmission target X-ray tube 50, and in addition make The higher dosage radiation 30 required with the lower-wattage to high voltage power supply 33, the air conditioner load saving with lower power demand BTU in relatively low thermal load, high voltage power supply 33, all lower operations for all having caused transmission target X-ray tube 20 at This.In addition, the hemispherical anode construction 22 for being configured with high surface area caused due to its heat-sinking capability it is cooling or colder or more The anode of low temperature, and therefore do not require any internal or external cooling system, such as rotary anode or with inner passage Therefore cooling fluid with the heat generated in anode construction 22 during operation that dissipates, and reduces transmission target X and penetrates The operating cost of spool 50.
Herein still it is still further contemplated that transmission and the radiation of reflectance target X-ray tube 50 30 may be used as biological cell spoke According to device, virally inactivated irradiator, insect irradiator, blood irradiator, food irradiator.
Foregoing description and drawings include the illustrative embodiments of the disclosure.Therefore exemplary embodiment has been described, Those of ordinary skill in the art, and can be within the scope of the invention it should be noted that internal use is merely exemplary Carry out various other replacements, reorganization and modification.It is only sequentially listed with certain or the step of method for numbering serial is not constituted to this method The step of sequence any restrictions.Those skilled in the art will expect many modifications and other embodiments of the invention, About its benefit of the invention with the introduction presented in the description and associated drawings of front.Although herein can be using spy Determine term, but they are only used for generic and descriptive sense, and is not intended to the purpose of limitation.In addition, having been described in The present invention；It should be understood that in the case where not departing from the spirit and scope of the present invention being defined by the following claims, Various changes, replacement and change can be carried out to it.Therefore, the present invention is not limited to specific embodiments shown in this article, but only It is limited by following following claims.

Claims (26)

1. a kind of X-ray tube for being accelerated under high-voltage potential to electronics, the X-ray tube include:
Shell；
Transmission and reflectance target anode construction, are set on the housing, the anode construction be configured with by The hemispherical at the center of the circle of 2D substrate creation；
Cathode construction is arranged in the shell, and the cathode construction is configured as making the electronics towards the anode knot Structure is deflected；
Filament is arranged in the shell, and the filament is positioned proximate to by the institute of the hemispheric 2D substrate creation State round center and between the anode construction and the cathode construction；
Wherein the evacuation shell is configured as the anode construction, the cathode construction and the filament vacuum wherein Sealing.
2. X-ray tube according to claim 1, wherein the anode construction is coated at least one object element, with Bremstrahlen X-ray is generated from the multiple acceleration electronics for being originated from the filament.
3. X-ray tube according to claim 1, wherein the anode construction by be substantially X-ray transparent material shape At.
4. X-ray tube according to claim 2, wherein being electroplated using evaporation or sputtering technology via electrochemistry plate, machine Tool in conjunction with or vapor deposition in one on the anode construction formed described at least one object element.
5. X-ray tube according to claim 3, wherein the material is by one or more groups in following composed group At: beryllium, carbon, aluminium, ceramics, stainless steel or its alloy.
6. X-ray tube according to claim 2, wherein the cathode construction generates electrostatic field, the electrostatic field will be originated from The multiple acceleration electronics of the filament is uniformly distributed at least one the described target element formed on the anode construction On element.
7. X-ray tube according to claim 6, wherein the X-ray tube generates symmetrical hemispheric transmission X-ray ?.
8. X-ray tube according to claim 7, wherein the X-ray tube generates transmission and reflection X-ray field.
9. X-ray tube according to claim 8, wherein adjusting linear between the anode construction and the cathode construction Distance is to change transmission and reflection X-ray field.
10. X-ray tube according to claim 9, wherein increasing the linear range to generate the described anti-of broad mode Penetrate transmission X-ray field.
11. X-ray tube according to claim 9, wherein reducing the linear range to generate the described anti-of narrow mode Penetrate transmission X-ray field.
12. X-ray tube according to claim 4, wherein at least one described object element has between 2 and 50 microns Thickness.
13. X-ray tube according to claim 4, wherein the X-ray tube generate by least one described object element and The output X-ray spectrum that cathode voltage determines.
14. X-ray tube according to claim 4, wherein the X-ray tube is generated by least one object element kαThe output X-ray spectrum that energy line and cathode voltage determine.
15. X-ray tube according to claim 12, wherein at least one object element thickness by cathode voltage and it is described extremely The transfer efficiency of a few object element is determined.
16. a kind of method for generating monochromatic output X-ray spectrum, the described method comprises the following steps:
The X-ray tube for being accelerated under high-voltage potential to electronics is provided, the X-ray tube includes:
The evacuation shell sealed；Transmission and transmission and reflection target anode structure on the housing, the anode is set Structure is configured with the hemispherical of geometric center；The cathode construction being arranged in the shell, the cathode construction quilt It is configured to deflect the electronics towards the anode construction；The filament being arranged in the shell, the filament quilt Be located close to by the circle of the hemispheric 2D substrate creation center and the anode construction and the cathode construction it Between, wherein directly being contacted by the circle that hemispheric 2D substrate creates with the cathode construction, and the wherein evacuation shell Body is configured as: wherein by the anode construction, the cathode construction and the filament vacuum sealing；To only lower than described The K of at least one object elementαThe output X-ray spectrum of energy is filtered；And
To the K for being only higher than at least one object elementαThe cathode voltage of energy is adjusted.
17. according to the method for claim 16, further including generating to have the output X-ray spectrum level of known spectra to be used for The step of analyzing X-ray application.
18. further including according to the method for claim 16, generating dual output X-ray spectrum with the step for image analysis Suddenly.
19. according to the method for claim 17, further including the steps that generating transmission and reflectance target exports X-ray spectrum.
20. according to the method for claim 17, further including the steps that generating reflectance target output X-ray spectrum.
21. further including according to the method for claim 17, by the k using selected at least one object elementα Line, the step of high-caliber output X-ray spectrum is generated with reduced cathode voltage.
22. according to the method for claim 16, further including the target output X-ray spectrum generated for biological cell irradiator The step of.
23. according to the method for claim 16, further including the target output X-ray spectrum generated for virally inactivated irradiator The step of.
24. according to the method for claim 16, further including the step for generating the target output X-ray spectrum for insect irradiator Suddenly.
25. according to the method for claim 16, further including the step for generating the target output X-ray spectrum for food irradiator Suddenly.
26. further including according to the method for claim 19, the line adjusted between the anode construction and the cathode construction The step of property distance is to change transmission and reflection X-ray field.
CN201811234524.1A 2017-10-23 2018-10-23 High dose delivery, transmission and reflection target X-ray system and method of use Active CN109698105B (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US15/709,426 US11101096B2 (en) 2014-12-31 2017-10-23 High dose output, through transmission and relective target X-ray system and methods of use
US15/709,426 2017-10-23

Publications (2)

Publication Number Publication Date
CN109698105A true CN109698105A (en) 2019-04-30
CN109698105B CN109698105B (en) 2021-08-10

Family

ID=66229762

Family Applications (1)

Application Number Title Priority Date Filing Date
CN201811234524.1A Active CN109698105B (en) 2017-10-23 2018-10-23 High dose delivery, transmission and reflection target X-ray system and method of use

Country Status (1)

Country Link
CN (1) CN109698105B (en)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN110942967A (en) * 2019-12-13 2020-03-31 中国工程物理研究院流体物理研究所 X-ray tube

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20130003931A1 (en) * 2011-06-29 2013-01-03 Tobias Funk Method and apparatus for localized x-ray radiation treatment
CN103311078A (en) * 2013-06-28 2013-09-18 上海轼辙仪器有限公司 X-ray tube
US20160189911A1 (en) * 2014-12-31 2016-06-30 Rad Source Technologies, Inc. High dose output, through transmission target x-ray system and methods of use

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20130003931A1 (en) * 2011-06-29 2013-01-03 Tobias Funk Method and apparatus for localized x-ray radiation treatment
CN103311078A (en) * 2013-06-28 2013-09-18 上海轼辙仪器有限公司 X-ray tube
US20160189911A1 (en) * 2014-12-31 2016-06-30 Rad Source Technologies, Inc. High dose output, through transmission target x-ray system and methods of use

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN110942967A (en) * 2019-12-13 2020-03-31 中国工程物理研究院流体物理研究所 X-ray tube
CN110942967B (en) * 2019-12-13 2022-07-15 中国工程物理研究院流体物理研究所 X-ray tube

Also Published As

Publication number Publication date
CN109698105B (en) 2021-08-10

Similar Documents

Publication Publication Date Title
US11521820B2 (en) Three-dimensional beam forming x-ray source
US9818569B2 (en) High dose output, through transmission target X-ray system and methods of use
US10068740B2 (en) Distributed, field emission-based X-ray source for phase contrast imaging
US7197116B2 (en) Wide scanning x-ray source
US5907595A (en) Emitter-cup cathode for high-emission x-ray tube
US10483077B2 (en) X-ray sources having reduced electron scattering
US20100189223A1 (en) Digitally addressed flat panel x-ray sources
US8054944B2 (en) Electron beam controller of an x-ray radiator with two or more electron beams
US11101096B2 (en) High dose output, through transmission and relective target X-ray system and methods of use
KR101151858B1 (en) X-ray generating apparatus having multiple targets and multiple electron beams
CN111448637A (en) MBFEX tube
US20160189907A1 (en) Longitudinal high dose output, through transmission target x-ray system and methods of use
CN109698105A (en) The transmission and reflectance target x-ray system and application method of high dose output
US7469040B2 (en) X-ray tube for high dose rates, method of generating high dose rates with X-ray tubes and a method of producing corresponding X-ray devices
WO2011044199A1 (en) Digitally addressed flat panel x-ray sources
US20140126702A1 (en) X-ray emitter
CN106409638A (en) Flat-plate type X ray source device with double surfaces radiating X rays simultaneously
CN101720492B (en) Device for generating X-ray radiation and having a large real focus and a virtual focus which are adjusted as required
RU2678326C1 (en) Ultra-compact x-ray emitter
CN212848300U (en) Radiation conversion target assembly for high dose yield circumferential irradiation tube
KR101631668B1 (en) X-ray source comprising cnt yarn using filtered arc deposition and x-ray emitting apparatus using the same
JP2004335419A (en) X-ray generator
CN111916325A (en) High dose yield circumferential irradiation ray tube
KR20240048994A (en) X-ray generator
CN114999876A (en) Cold cathode X-ray source and application thereof

Legal Events

Date Code Title Description
PB01 Publication
PB01 Publication
SE01 Entry into force of request for substantive examination
SE01 Entry into force of request for substantive examination
GR01 Patent grant
GR01 Patent grant