[go: up one dir, main page]
More Web Proxy on the site http://driver.im/

CN103094030A - Transmission type x-ray tube and reflection type x-ray tube - Google Patents

Transmission type x-ray tube and reflection type x-ray tube Download PDF

Info

Publication number
CN103094030A
CN103094030A CN2012101841842A CN201210184184A CN103094030A CN 103094030 A CN103094030 A CN 103094030A CN 2012101841842 A CN2012101841842 A CN 2012101841842A CN 201210184184 A CN201210184184 A CN 201210184184A CN 103094030 A CN103094030 A CN 103094030A
Authority
CN
China
Prior art keywords
ray
ray tube
penetration
filtering material
target
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.)
Pending
Application number
CN2012101841842A
Other languages
Chinese (zh)
Inventor
布鲁斯·布莱恩特·帕森斯
郑积杰
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.)
GAMC BIOTECH DEVELOPMENT CO LTD
Original Assignee
GAMC BIOTECH DEVELOPMENT 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 TW100139390A external-priority patent/TWI555511B/en
Application filed by GAMC BIOTECH DEVELOPMENT CO LTD filed Critical GAMC BIOTECH DEVELOPMENT CO LTD
Priority to CN201810074133.1A priority Critical patent/CN108321070A/en
Publication of CN103094030A publication Critical patent/CN103094030A/en
Pending legal-status Critical Current

Links

Images

Classifications

    • 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
    • H01J35/18—Windows
    • H01J35/186—Windows used as targets or X-ray converters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/508—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for non-human patients
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2235/00—X-ray tubes
    • H01J2235/08—Targets (anodes) and X-ray converters
    • H01J2235/081—Target material
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00—X-ray tubes
    • H01J35/02—Details
    • H01J35/04—Electrodes ; Mutual position thereof; Constructional adaptations therefor
    • H01J35/08—Anodes; Anti cathodes
    • H01J35/112—Non-rotating anodes
    • H01J35/116—Transmissive anodes

Landscapes

  • X-Ray Techniques (AREA)
  • Apparatus For Radiation Diagnosis (AREA)

Abstract

The invention discloses a transmission X-ray tube and a reflection X-ray tube. The target material comprises at least one element, and X-ray generated after the element is excited comprises radiation energy of K alpha and K beta, and can irradiate an object for radiography. The filter material is transparent to the X-rays, the filter material having a K-edge absorption energy that is higher than the K α radiation energy of the element but lower than the K β radiation energy of the element. The thickness of the filter material is at least 10 micrometers and less than 3 millimeters.

Description

Penetration X-ray tube and reflective X-ray tube
Technical field
The present invention relates to a kind of penetration X-ray tube and a kind of reflective X-ray tube, relating in particular to can be by a kind of penetration X-ray tube and a kind of reflective X-ray tube of filtering material with unnecessary radiation filtering.
Background technology
In the medical science angiographic method of employing with the low Z filtering material of the materials such as aluminium, molybdenum, yttrium and copper, can reduce low-energy ray by so-called aluminium equivalent filter thickness.Basically, the scope of the equivalent thickness of this aluminium filtering material is the 0.5-12 micron,, long wavelength's low-yield in order to filter X-ray, and reduce may the harmful and unnecessary radiation to the medical science radiography.Unfortunately, such filter also filters out most useful X-ray.
Nondestructive test can separately not add the filtering material usually, but when will be with the ray of specific K α line, and when providing high-quality image to the article that carry out the nondestructive test radiography, removing unnecessary high-octane photon is also one of purpose of the present invention.
In the medical science radiography, chemical radiography element is for example the compound that contains iodine, gadolinium, barium, can produce high contrast to the soft tissue of periphery because of its density and atomicity.The importance of the atomicity of these elements (Z=53 of iodine, the Z=56 of barium, the Z=64 of gadolinium) is, with respect to traditional X-ray energy spectrum, K absorption edge value is to be positioned at better being with.The K marginal value of iodine is 33.17keV (kilo electron volt), and the K marginal value of barium is 37.44keV, and the K marginal value of gadolinium is 50.24keV.During slightly higher than the K edge energy of chemical contrast agent, can produce maximum contrast when the X-ray photon energy.
In the special medical program, the selection of best spectrum will consider to be not only the demand of contrast, also will consider can produce necessary penetrability and the received radiation dose of limiting patient to body part.
Different industrial products, including but not limited to electronic circuit, integrated circuit, light-emittingdiode and the lithium battery of all kinds in the case of non-destructive radiography, all can have a single optimum capacity that can produce the largest image quality.Yet for the optimum capacity of output high light flux, inevitably simultaneously also can produce the photon that higher-energy is arranged higher than optimum capacity.The photon of higher-energy is unnecessary, and they can reduce the contrast of image.On the other hand, when too many unnecessary X-ray was radiated on inductor, the inductor overload can be another problem.
For reflective X-ray tube, the spectrum of X-ray bundle be by anode material, filtering material and thickness thereof and in this program the combination of selected tube voltage determined.The thickness of target is not important problem.
It is an X-ray spectrum that is positioned on narrow and well-defined photonic band gap and has a large amount of photons that the X-ray radiography is used upward needed, and utilize the filtering of filtering material those have energy higher than and or lower than this can with photon, and required this of the maximization image quality of as far as possible avoiding detracting can with luminous flux.Useful can be with energy higher than this can with flux ratio should be maximized in the heat radiation limit of X-ray tube.For the application of medical science radiography, reduce simultaneously unnecessary energy photons and the obvious dosage that reduces for patient, will obviously can provide extra benefit.For the radiography of lifeless object, the energy of photon can hang down to 15 to 20keV, and general medicine radiography photon energy is near 30keV, and high-energy radiography photon energy is up to 600keV.
This filters solutions can be used reflective and the penetration X-ray tube.When using the penetration X-ray tube, necessary mode is to allow the ratio optimization of amount of photon of the amount of useful X-ray and higher-energy.In medical applications, necessary mode is to allow the dosage of useful X-ray and the dosage optimization that patient absorbs, and will reduce simultaneously the amount of the photon high than the energy of available energy band.Utilizing the thickness of target can't make the luminous flux optimization of reflective X-ray tube, therefore, is limited by the composition of adjusting thickness or filtering material to reach the result of wanting.
Summary of the invention
The invention provides a kind of penetration X-ray tube, can be by the filtering material with unnecessary radiation filtering.
The invention provides a kind of reflective X-ray tube, can be by the filtering material with unnecessary radiation filtering.
The invention provides a kind of penetration X-ray tube, this penetration X-ray tube comprises a target and a filtering material.This target comprises at least one element, and the be stimulated X-ray of rear generation of this element comprises the emittance of K α and K β, can shine an object and carry out radiography.This filtering material can be passed by this X-ray, and this filtering material has a k edge and absorbs energy, and this k edge absorbs energy higher than the K α emittance of this element, but lower than the K β emittance of this element.The thickness of this filtering material is at least 10 microns and be less than 3 millimeters.
In one embodiment of this invention, this target comprises scandium, titanium, vanadium, chromium, manganese, iron, cobalt, nickel, copper, zinc, germanium, yttrium, niobium, molybdenum, ruthenium, rhodium, palladium, silver, tin, barium, lanthanum, cerium, neodymium, gadolinium, terbium, dysprosium, holmium, erbium, thulium, ytterbium, gold-plating, hafnium, tantalum, tungsten, rhenium, iridium, platinum, gold, thorium, uranium or its combination, or by comprising above-mentioned material or the formed element of its combination, compound, alloy, intermetallic compound or composite material.
In one embodiment of this invention, this filtering material comprises titanium, yttrium, gadolinium, ruthenium, vanadium, samarium, neodymium, thorium, holmium, palladium, cobalt, cerium, niobium, tantalum, molybdenum, copper, chromium, iridium, erbium, rhodium, europium, indium, hafnium, rubidium, thulium, zinc, antimony, terbium, zirconium, manganese, tin, rhenium, strontium, tungsten, nickel, cadmium, gallium, technetium, gold-plating, dysprosium, iron, ytterbium or its combination, or by comprising above-mentioned material or the formed element of its combination, compound, alloy, intermetallic compound or composite material.
In one embodiment of this invention, the thickness of above-mentioned target is between 5 to 500 microns.
In one embodiment of this invention, above-mentioned penetration X-ray tube is as the microscopical X-ray light source of an X-ray.
In one embodiment of this invention, above-mentioned penetration X-ray tube is the image that obtains the medical science radiography.
The invention provides a kind of reflective X-ray tube, this reflective X-ray tube comprises a target and a filtering material.This target comprises at least one element, and the be stimulated X-ray of rear generation of this element comprises the emittance of K α and K β, can shine an object and carry out radiography.This filtering material can be passed by this X-ray, and this filtering material has a k edge and absorbs energy, and this k edge absorbs energy higher than the K α emittance of this element, but lower than the K β emittance of this element.The thickness of this filtering material is at least 10 microns and be less than 3 millimeters.
In one embodiment of this invention, above-mentioned reflective X-ray tube is as the microscopical X-ray light source of an X-ray.
In one embodiment of this invention, above-mentioned reflective X-ray tube is the image that obtains the medical science radiography.
When the energy of the contained photon of the X-ray photon beam k marginal value just above a filtering material, this material will absorb this specific photon beam consumingly.If find that the absorption edge of a filtering material is between the K α and K β line of incident X-ray photon beam, this material can be used for reducing significantly K β line with respect to the intensity of K α line so, so this material is defined as K β filtering material.
The present invention discloses a penetration X-ray tube, the target thickness of this X-ray tube is the 5-500 micron, can with selected many K β filtering combinations of materials, to provide simultaneously with unnecessary high-energy and unnecessary low-energy X-ray filtering, the high-octane X-ray of filtering can improve image quality, and the low-yield X-ray of filtering can reduce the dosage that patient absorbs in medical applications.
Same a kind of reflective X-ray tube and a kind of filtering material that is applied to medical radiography and nondestructive test radiography that disclose of the present invention, this filtering material is with respect to such as being the low Z filtering materials such as aluminium or copper, dosage can be reduced to a quite low dosage and can obviously not reduce the X-ray useful to radiography, and the high-energy photons more than the target k line that reduces simultaneously at reflective X-ray tube.
The target of thick penetration X-ray tube and the target of reflective X-ray tube are to be selected from following possible material, and these materials include but not limited to scandium, titanium, vanadium, chromium, manganese, iron, cobalt, nickel, copper, zinc, germanium, yttrium, niobium, molybdenum, ruthenium, rhodium, palladium, silver, tin, barium, lanthanum, cerium, neodymium, gadolinium, terbium, dysprosium, holmium, erbium, thulium, ytterbium, gold-plating, hafnium, tantalum, tungsten, rhenium, iridium, platinum, gold, thorium or uranium.
About 10 microns to 3 millimeters of the thickness of the different K β filtering material that these are chosen.
K β filtering material of the present invention can be used for forming the radiography of medical science radiography and nondestructive test, the medical science radiography includes but not limited to patient's breast, the thoracic cavity, the joint, four limbs, skull, belly, intestines and stomach, the image precise positioning of guiding high energy radiation treatment or the location of carrying out this kind treatment in the patient body, and the object of the radiography of nondestructive test includes but not limited to circuit board, the solder ball array circuit, the distributing electronic component, MEMS (micro electro mechanical system) (MEMS) device, toy, organic and geological sample, semiconductor wafer package, and numerous other are used for the lifeless object of Different Industries.In many nondestructive tests were used, these X-ray tubes and the K β filtering material that includes thereof can be applicable to the microscopical X-ray light source of X-ray.
The invention relates to a kind of radiography of X-ray, although it is mainly the significant problem that solves the medical science radiography, the aspect that also can be applied in other comprises the nondestructive X-ray radiography of lifeless object.The present invention can be applicable to use the X-ray radiography of reflective X-ray tube, penetration X-ray tube, solid target pipe and rotating-anode tube, and the X-ray of all energy in medical science and nondestructive test radiography.The present invention discloses a kind of method, reduces the X ray that can be with below or above useful X-ray in the X-ray tube output spectrum.In the application of X-ray, need highdensity monochromatic X-ray, and the present invention discloses thick penetration that a kind of employing has K β filtering material or the composition of reflective target, the thickness of this K β filtering material will make the K β ray of X-ray target obviously reduce.On using, the present invention uses the X-ray tube of filtering material can be in order to provide the microscopical standard of X-ray monochromatic X-ray light source.
For above-mentioned feature and advantage of the present invention can be become apparent, embodiment cited below particularly, and coordinate appended graphic being described in detail below.
Description of drawings
Fig. 1 is the schematic diagram of the one penetration X-ray tube according to the present invention, and this penetration X-ray that X-ray tube produces is through filtering.
Fig. 2 is the schematic diagram of the one reflective X-ray tube according to the present invention, and X-ray that this reflective X-ray tube produces is through filtering.
Fig. 3 is the output spectrum that shows a penetration X-ray tube, and this penetration X-ray tube has a metal gadolinium target and filters X-ray by aluminium and copper.
Fig. 4 is the output spectrum that shows a penetration X-ray tube, and this penetration X-ray tube has the metal gadolinium target of one 20 micron thickness and without the filtering material.
Fig. 5 is the output spectrum that shows a penetration X-ray tube, and this penetration X-ray tube has a metal gadolinium target and has the filtering material of a samarium metal.
Fig. 6 is the spectrum that shows a penetration X-ray tube, and this penetration X-ray tube has a thick metal tantalum target and filters with traditional high Z materials.
Fig. 7 is when being presented at without the filtering material, the spectrum of the metal tantalum penetration target of one 50 micron thickness and the metal tantalum target of one 100 micron thickness.
Fig. 8 is the output spectrum that shows a penetration X-ray tube, and this penetration X-ray tube has thickness 100 micron metal tantalum targets and has the filtering material of the metallic ytterbium of 80 microns of thickness.
Fig. 9 is the output spectrum that shows a reflective X-ray tube, and this reflective X-ray tube is that the low Z value filtering material with standard filters, and compares with the spectrum of the metallic ytterbium filtering material that adds 80 micron thickness.
Figure 10 is the penetration X-ray tube output after filtering that shows a metal molybdenum target, and this penetration X-ray tube has a metal niobium filtering material.
Figure 11 be show a penetration X-ray tube three different-thickness and by thulium the output spectrum under metal filtering material, this penetration X-ray tube has a tantalum metal targets.
Reference numeral:
1: end window anode
2: the target tinsel
3,12: negative electrode
4,10: electron beam path
5: the selectivity Focusing mechanism
6: power supply unit
7: vaccum case
8:X light
11: side window
The 13:X light beam
14: anode
17～36: output spectrum
Embodiment
The penetration X-ray tube of Fig. 1 has comprised a vaccum case 7 and has been arranged on housing 7 ends and has been exposed to an end window anode 1 in atmosphere.One 2 of X-ray target tinsels are positioned on end window anode 1.In the window of the end of some X-ray tubes, the X-ray target is to make with identical material with the end window, avoids X-ray to pass the problem of different ends window material.When a thicker strong vacuum to being enough to support X-ray tube of target, different end window materials are unnecessary.One electronics or the negative electrode of photon excitation 3 penetrates electronics, and these electrons are accelerated and hit anode target material and produce X-ray along electron beam path 4.Power supply unit 6 is connected between negative electrode and anode to provide accelerative force to electron beam.The X-ray 8 that produces passes through the end window and the effusion X-ray tube.One optionally Focusing mechanism 5 be to utilize electrical bias voltage basically, make Electron Beam Focusing upwards, or focus on a point of target downwards.This size in the target material surface maximum is almost namely the size of focus.X-ray has comprised the radiation of K α and K β characteristic, and it has unique association at least one element in target.In a preferred embodiment of the present invention, have the penetration X-ray tube that target thickness reaches 5 microns or 200 microns and be positioned on an end window.When target tinsel and end window were identical material, its thickness can reach 500 microns.In a preferred embodiment of the present invention, be by the K β filtering material of thickness from 10 microns to 3 millimeters, the output radiation of one penetration X-ray tube to be filtered.
Fig. 2 is the schematic diagram of a reflective X-ray tube, includes a vaccum case, and wherein a negative electrode 12 and an anode 14 are arranged in vaccum case.Anode 14 comprises that one is arranged on the X-ray target on a substrate, the heat energy that produces during the removable X-ray irradiation of substrate anode.Electronics is penetrated by negative electrode.One power supply unit 6 is connected between anode and negative electrode, in order to an electric field to be provided, accelerate along 10 pairs of electronics that penetrated by negative electrode of an electron beam path, make a point of electronic percussion anode 14, and producing an X-ray bundle 13, this X-ray bundle 13 is penetrated from X-ray tube via a side window 11.Electron beam irradiation is on target, and reflective X-ray tube can be collected from the same side of target the X-ray of generation.The X-ray that produces by target is radiated on object to produce image, and the ray of the K α that this X-ray comprises simultaneously and K β character has unique correlation at least one element in target.In a preferred embodiment of the present invention, the output of a penetration X-ray tube is filtered by a K β filtering material, and the thickness of K β filtering material is between 10 microns to 3 millimeters.
Open penetration X-ray tube is for the radiography to electronic circuit and the application of other high-ress basically, and when the image of object needs higher multiple, can be used as substituting X-ray light source.The penetration X-ray tube of sealing seals vacuum, and penetration X-ray tube open or that bleed has a vacuum pumps in order to be evacuated continuously, the pipe fitting that usually can't operate in order to frequent replacement.For reaching purpose of the present invention, the penetration X-ray tube comprises penetration X-ray tube open and sealing simultaneously, but gets rid of the part of exception explanation.
Unless stated otherwise, otherwise the SPECTRAL DATA of specific X-ray tube is measured by the equipment of the Amptek model XR-100 of company, and this equipment has cadmium tellurium sensor and the thick beryllium filtering material of 10mils (mil) that 1mm is thick.The distance X light pipe that arranges of sensor has 1 meter, and different X-ray tube electric currents and different time for exposure are adopted in experiment.
Make the k absorption edge value of element of K β filtering material between the K of X-ray target α line and K β line, this X-ray target can be used for a penetration X-ray tube or a reflective X-ray tube.Following table 1 describes for the target that each may adopt, and these materials can form a suitable K β filtering material of the present invention.
Table 1: in order to the various materials as the K β filtering material of penetration X-ray tube
Figure BDA00001732810000081
Figure BDA00001732810000091
Figure BDA00001732810000101
Fig. 3 represents that one has the penetration X-ray tube that a gadolinium target is 20 micron thickness.The voltage that this X-ray tube is applied is 80kVp (kilovolt peak).Label 17 expression is except the filtering of thick gadolinium target itself and the output spectrum of the X-ray tube of non-filtered.Although the thickness of target is 20 microns, the thickness of target can be from being less than 5 microns to the hundreds of micron.Output spectrum after label 18 expressions X-ray tube same as described above filters via an aluminium filtering material that hangs down Z value 1.5 millimeters thick.Output spectrum after label 19 expression is filtered via the aluminium equivalent thickness of one 9 millimeters.Use the filtering mode of target gadolinium and traditional low Z value that low dosage and the luminous flux of abundance simultaneously can't be provided, can use the image contrast agent of iodine for example or barium.
Fig. 4 represents to have the gadolinium target of 20 microns of thickness and apply tube voltage 80kVp (label 20) and the output spectrum of the penetration X-ray tube of 90kVp (label 21) by one, this output spectrum there is no by other filtering material and filters except through the thick filtration that penetrates target own.The X-ray that the gadolinium target produces can be used for the developing developer of barium is because when 42.7kev (the K α value of gadolinium), the mass-absorption coefficient of barium is 22.4cm2/gm.The X-ray that the gadolinium target produces also can be used for the developing developer of iodine, because when 42.7kev, the mass-absorption coefficient of iodine is 18.46cm2/gm.Gadolinium is one and produces K α radiation extraordinary source, can provide obvious contrast by the developer to any barium and iodine when carrying out radiography.By the thickness that increases the gadolinium target, can reach extra self filter action for output spectrum, and useful luminous flux only has the impairment of small part under 42.7kev.
Fig. 5 is explanation the present invention one preferred embodiment.Reference table 1, samarium metal can be regarded a kind of filtering material of tool two K β values as.Utilize the samarium of 50 microns of thickness to filter the output spectrum of the gadolinium target of above-mentioned its 20 micron thickness of penetration X-ray tube.Fig. 5 represents that samarium filtering material is applied in the data on the gadolinium output spectrum, and wherein tube voltage is 90kVp.Label 22 is presented at the spectrum of gadolinium target filtered under tube voltage 90kVp.Label 23 show the K β filtering material samarium of 50 micron thickness how to reduce each can with number of photons.The K α of gadolinium can be with and only reduce 10%, and 40-50kev (the K β value of gadolinium is 48.69) can with on energy nearly reduced 40%.In lower than the 35kev photon energy, number of photons reduces 58%, the suffered radiation dose of patient is obviously reduced, and reduced by 30% in the output energy of 45kev to 90kev, reduce the situation of the contrast degeneration that undesired high-energy photons causes in angiographic procedure.Although be that the thickness of target can be from 5 microns to 200 microns with the metal gadolinium target of 20 microns of thickness as an example at this.The thickness of filtering material can reduce to 10 microns and its result has less filtration but stronger K α output, perhaps, if the gadolinium target has 100 micron thickness or thicker, the thickness of filtering material can thickly reach 3 millimeters, and the accelerating voltage of this X-ray tube can be up to 150kVp.
Fig. 6 is the representative graph of the output spectrum of a penetration X-ray tube, and wherein the penetration X-ray tube has the tantalum metal targets of one 75 micron thickness, operates under tube current 50 micromicroamperes, and has 9 millimeters equivalent aluminium filtering materials that basically are applied to medical radiography.The label 24 unfiltered output spectrums of expression, and the output spectrum that label 25 expressions are filtered by a low Z value filtering material, this low Z value filtering material has these 9 millimeters equivalent aluminium filtering materials.From 0 to 40kev low-energy light subband, the X-ray photon has reduced 60.5%, reduces significantly useless low-yield X-ray, avoids patient is caused radiation injury.Yet scope useful X-ray between 40 to 70kev has reduced by 60% simultaneously.The X-ray of the contrast of meeting impairment image has reduced 26.7% more than 70kev.Yet, having reduced 60% compared to useful X-ray, the high-energy X-ray is to have accounted for higher ratio.The ratio of high-octane X-ray in unfiltered output spectrum by 12.2% be increased in the output spectrum that has filtered 19.3%.Therefore, though the filtering material of low Z value can reduce the radiation dose that patient absorbs effectively, also reduced most of useful X-ray simultaneously.After having used the filtering material, make the effect variation of the high-energy photons about about 70kev greatly.
Therefore it should be noted that the penetration X-ray tube of the penetration target with one 75 micron thickness, because X-ray must pass thick target before the effusion window, can obviously reduce low-energy radiation by itself to the filtration of X-ray.
Although make comparisons lower than the X-ray photon energy of 40kev for energy, for obtaining high-quality image, the application of the X-ray of energy between 30 to 40kev is also extremely important.Similarly, select arbitrarily the useful X-ray energy of 40-70kev to show concept of the present invention.Medically or in nondestructive test, the application of each radiography all can have itself for the definition of useful or useless x-ray.Under the restriction of feasible tube current, the technology of filtering of the present invention will be used to making useful X-ray optimization, and reduce X-ray photon not, that can't contribute to X-ray radiography quality.
Table 2
Figure BDA00001732810000121
Fig. 7 illustrates that one has self filtering characteristic of the penetration X-ray tube of thick target material sheet metal.The spectrum of label 26 expression one penetration X-ray tubes, this X-ray tube has the target of 50 microns of thickness.The spectrum of label 27 expression one penetration X-ray tubes, this X-ray tube has the target of 100 microns of thickness.Above-mentioned two X-ray tubes are all to operate under 100kVp and 50mA.Above table 2 summarize each X-ray tube less than being with of 40kev, 40 to 70kev can be with and 70 to 100kev can be with in number of photons.
Wherein useful X-ray has detracted approximately 34.5% in being with of 40-70kev, and can be with the X-ray that is considered to increase patient irradiation dose lower than 40kev to reduce 72%.In addition, can be with the X-ray at 70-100kev to reduce 48%, obvious loss more than useful X-ray.
In a preferred embodiment of the present invention, add a filtering material on the target of 100 microns of existing tool self filtrations, thickness.The filtering material that is selected from table 1 can be gold-plating, thulium, ytterbium one of them.Fig. 8 be illustrated in the spectrum of a penetration X-ray tube each can with number of photons, wherein this X-ray tube has the tantalum metal targets of 100 micron thickness, and operates under tube voltage 100kVp and tube current 50 micromicroamperes.Label 28 expressions are without the data that adds the filtering material, and the output spectrum that label 29 shows after the ytterbium metal filtering filtration of material of 80 microns of thickness.Following table 3 is concluded the difference between two spectrum.
Table 3
Figure BDA00001732810000131
The amount of energy undesired X-ray number of photons below 40kev has lacked 68.7% extraly, and so making for patient has the radiation dose of injury obviously to reduce.This one reduces the relative energy that makes and has reduced 29.4% in the amount of 40 to 70kev useful X-ray number of photons, but the percentage that the dosage below 40kev reduces with respect to energy, and the percentage that useful X-ray reduces is quite few.Cause the energy loss of useful X-ray due to ytterbium metal filtering material, also produce the net loss of photon numbers at energy higher than the part of 70kev.Be not presented among Fig. 8, contributed by useful X-ray the part that has more, this is because (the k marginal value of ytterbium metal) absorbed energy is converted into the X-ray of the K α of ytterbium metal more than 61.332kev, because when the ytterbium atom sends fluorescent, the ytterbium metal has the K α value of a 52.4kev.Use together with the tantalum target of the ytterbium filtering material of 80 microns of thickness and 100 microns of thickness is under voltage 100kVp, this is only a mode of filtering principle as explaining, this kind filters principle can utilize different filtering materials, different X-ray tube voltage, different filtering material thickness, different penetration target thickness and different penetration targets, and develop the scheme of a cover filtering, obviously be better than utilizing low Z value material to carry out the filtration of X-ray to carry out the X-ray radiography such as copper and aluminium.
When abiotic object utilized X-ray of the present invention to carry out radiography, more emphasis was to be, its its energy of X-ray that provides is higher than being less in order to the part that produces the required X-ray of high-quality image.These higher energy can reduce the contrast of image.
In another preferred embodiment of the present invention, be to have illustrated by having the tungsten metal targets and utilizing traditional copper and the low Z value material such as aluminium carries out the output spectrum that a reflective X-ray tube of filtering produces.Utilize atomicity lower but provide quite efficient filter action near the filtering material of the high Z value of target, make the dosage of useful radiation that minimum loss be arranged.
Fig. 9 represents the distribution map of the X-ray flux of a conventional reflective X-ray tube.Label 31 represents the spectrum output map of a reflective X-ray tube, and this reflective X-ray tube has a tungsten target material and operates under tube voltage 120kVp and tube current 3Ma.This output spectrum is to filter via the low Z value filtering material of the tradition that is equivalent to 9mm aluminium.Label 30 shows that utilizing the present invention's one filtering material to carry out further wavelength filters the rear result of calculating.Reference table 1, the filtering material of corresponding tungsten comprises hafnium, gold-plating, ytterbium and thulium.Select metallic ytterbium as the filtering material, thickness is 80 microns.Select a Z value higher than the target of metallic ytterbium from table 1, can allow energy originally export the state that is converted to a higher-energy.
Table 4 clearly illustrates that energy has further reduced 74.8% lower than the number of photons of 40kVp, and certain degree has reduced the radiation dose of the X-ray that patient receives, and the amount of useful X-ray only reduces 38%.Although obtaining of these data is to adopt low Z value filter method of the present invention and filtering technique, the filter method of this low Z value can be replaced with a kind of filtering material proposed by the invention, and the improvement of pretty good efficient is arranged.This filtering material will send the k line fluorescent radiation of self, and these fluorescent radiations also are not included among Fig. 9, and Fig. 9 shows the general output that only is increased in the photon in useful scope 40-70kVp, and reduce the amount of tube current, to obtain the image of same quality.
Table 4
In a preferred embodiment of the present invention, a K β filtering material that is complementary with the target of penetration X-ray tube or reflective X-ray tube is in order to the X-ray light source as medical radiography, and this medical radiography includes but not limited to patient's breast, thoracic cavity, joint, four limbs, skull, belly, intestines and stomach, the image precise positioning of guiding high energy radiation treatment or the location of carrying out this kind treatment in the patient body.
In another preferred embodiment of the present invention, a K β filtering material that is complementary with the target of penetration X-ray tube or reflective X-ray tube is in order to the accurate monochromatic X-ray light source as the radiography of the nondestructive test of material and biological specimen, material and biological specimen include but not limited to circuit board, solder ball array circuit, distributing electronic component, MEMS (micro electro mechanical system) (MENS) device, light-emittingdiode, lithium battery, toy, organic and geological sample, semiconductor wafer package, and numerous other are used for lifeless objects of Different Industries.Numerous application comprises as the microscopical X-ray light source of X-ray.
Figure 10 represents one embodiment of the invention.It is 60kVp that the one penetration X-ray tube with metal molybdenum target of one 50 micron thickness measures its tube voltage.In the situation that do not add the filtering material, 13,409 of number of photons and K β number of photons that the spectrum 32 of metal molybdenum X-ray tube has comprised K α are 4,076.When the metal niobium filtering material of other one 50 micron thickness is installed up, this metal niobium filtering material is be selected from table 1 and as K β filtering material, can calculate K α radiant light subnumber and reduce to 5,862, and K β radiant light subnumber reduce to 98.Adopt the niobium K β filtering material of 50 microns of thick metal molybdenum penetration X-ray tube and thickness, the radiation of K α can reduce 2.2 times in spectrum 33, and the radiation of K β can reduce 41.6 times.
For being with 32 only to have 37 number of photons from the whole of 20-25kev.This expression has produced a very consummate monochromatic K α radiation from a metal molybdenum X-ray tube.Although this be with metal molybdenum and metal niobium as an example, also can adopt any material in other targets and K β filtering material in table 1.
Figure 11 is the output light flux that shows the present invention's one penetration X-ray tube, the filtering material that this penetration X-ray tube has the tantalum metal targets of one 50 micron thickness and three different K β values of the present invention and made by thulium, wherein tube voltage is 90kVp, and tube current 50 is 50 micromicroamperes.After these filtering materials are installed, spectrum is measured.These three filtering material thicknesses are respectively 25 microns (labels 34), 50 microns (label 35) and 75 microns (label 36).Compare the amount of undesired K β luminous flux and energy photons, comprising major part from 15 to 40kev can't be in order to the dosage of radiography, the amount of the x-ray of useful K α after following table 5 explanations are filtered.
Table 5
Figure BDA00001732810000151
When the thickness of metal thulium filtering material increased to 75 microns by 25 microns, it is about 22% that useful K alpha ray only reduces, compared to undesired K β ray and from 15 to 40kev more low-yield, approximately reduced respectively 40% and about 43%.By the single filtering material of the present invention, can reach the photon amount idea that reduces energy photons and high K β value, the present invention can provide for the dosage that patient receives obvious improvement.Here the material thickness that adopts is only purpose as an illustration, and what understand very much is to use the filtering material of different-thickness can produce different effects.The impairment of any useful X-ray energy can increase pipe stream and be compensated by mat.In allowed limits, the increase of tube current has its restriction, can look the gross energy on the focus on the target that is radiated at the penetration X-ray tube.
Although the present invention discloses as above with embodiment, so it is not to limit the present invention, and any person of an ordinary skill in the technical field when can do a little change and retouching, and does not break away from the spirit and scope of the present invention.

Claims (11)

1. penetration X-ray tube comprises:
One target comprises at least one element, and the be stimulated X-ray of rear generation of this element comprises the emittance of K α and K β, can shine an object and carry out radiography; And
One filtering material can be passed by this X-ray, and this filtering material has a k edge and absorbs energy, and this k edge absorbs energy higher than the K α emittance of this element, but lower than the K β emittance of this element;
Wherein the thickness of this filtering material is at least 10 microns and be less than 3 millimeters.
2. penetration X-ray tube according to claim 1, wherein this target comprises scandium, titanium, vanadium, chromium, manganese, iron, cobalt, nickel, copper, zinc, germanium, yttrium, niobium, molybdenum, ruthenium, rhodium, palladium, silver, tin, barium, lanthanum, cerium, neodymium, gadolinium, terbium, dysprosium, holmium, erbium, thulium, ytterbium, gold-plating, hafnium, tantalum, tungsten, rhenium, iridium, platinum, gold, thorium, uranium or its combination, or by comprising above-mentioned material or the formed element of its combination, compound, alloy, intermetallic compound or composite material.
3. penetration X-ray tube according to claim 1, wherein this filtering material comprises titanium, yttrium, gadolinium, ruthenium, vanadium, samarium, neodymium, thorium, holmium, palladium, cobalt, cerium, niobium, tantalum, molybdenum, copper, chromium, iridium, erbium, rhodium, europium, indium, hafnium, rubidium, thulium, zinc, antimony, terbium, zirconium, manganese, tin, rhenium, strontium, tungsten, nickel, cadmium, gallium, technetium, gold-plating, dysprosium, iron, ytterbium or its combination, or by comprising above-mentioned material or the formed element of its combination, compound, alloy, intermetallic compound or composite material.
4. penetration X-ray tube according to claim 1, wherein the thickness of this target is between 5 to 500 microns.
5. penetration X-ray tube according to claim 1, this penetration X-ray tube are as the microscopical X-ray light source of an X-ray.
6. penetration X-ray tube according to claim 1, this penetration X-ray tube is the image that obtains the medical science radiography.
7. reflective X-ray tube comprises:
One target comprises at least one element, and the be stimulated X-ray of rear generation of this element comprises the emittance of K α and K β, can shine an object and carry out radiography; And
One filtering material can be passed by this X-ray, and this filtering material has a k edge and absorbs energy, and this k edge absorbs energy higher than the K α emittance of this element, but lower than the K β emittance of this element;
Wherein the thickness of this filtering material is at least 10 microns and be less than 3 millimeters.
8. reflective X-ray tube according to claim 7, wherein this target comprises scandium, titanium, vanadium, chromium, manganese, iron, cobalt, nickel, copper, zinc, germanium, yttrium, niobium, molybdenum, ruthenium, rhodium, palladium, silver, tin, barium, lanthanum, cerium, neodymium, gadolinium, terbium, dysprosium, holmium, erbium, thulium, ytterbium, gold-plating, hafnium, tantalum, tungsten, rhenium, iridium, platinum, gold, thorium, uranium or its combination, or by comprising above-mentioned material or the formed element of its combination, compound, alloy, intermetallic compound or composite material.
9. reflective X-ray tube according to claim 7, wherein this filtering material comprises titanium, yttrium, gadolinium, ruthenium, vanadium, samarium, neodymium, thorium, holmium, palladium, cobalt, cerium, niobium, tantalum, molybdenum, copper, chromium, iridium, erbium, rhodium, europium, indium, hafnium, rubidium, thulium, zinc, antimony, terbium, zirconium, manganese, tin, rhenium, strontium, tungsten, nickel, cadmium, gallium, technetium, gold-plating, dysprosium, iron, ytterbium or its combination, or by comprising above-mentioned material or the formed element of its combination, compound, alloy, intermetallic compound or composite material.
10. reflective X-ray tube according to claim 7, this reflective X-ray tube are as the microscopical X-ray light source of an X-ray.
11. reflective X-ray tube according to claim 7, this reflective X-ray tube is the image that obtains the medical science radiography.
CN2012101841842A 2011-10-28 2012-06-06 Transmission type x-ray tube and reflection type x-ray tube Pending CN103094030A (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
CN201810074133.1A CN108321070A (en) 2011-10-28 2012-06-06 Transmission type X-ray tube and reflection type X-ray tube

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
TW100139390A TWI555511B (en) 2010-12-07 2011-10-28 A transmission tpye x-ray tube and a reflection type x-ray tube
TW100139390 2011-10-28

Related Child Applications (1)

Application Number Title Priority Date Filing Date
CN201810074133.1A Division CN108321070A (en) 2011-10-28 2012-06-06 Transmission type X-ray tube and reflection type X-ray tube

Publications (1)

Publication Number Publication Date
CN103094030A true CN103094030A (en) 2013-05-08

Family

ID=48093177

Family Applications (2)

Application Number Title Priority Date Filing Date
CN2012101841842A Pending CN103094030A (en) 2011-10-28 2012-06-06 Transmission type x-ray tube and reflection type x-ray tube
CN201810074133.1A Pending CN108321070A (en) 2011-10-28 2012-06-06 Transmission type X-ray tube and reflection type X-ray tube

Family Applications After (1)

Application Number Title Priority Date Filing Date
CN201810074133.1A Pending CN108321070A (en) 2011-10-28 2012-06-06 Transmission type X-ray tube and reflection type X-ray tube

Country Status (3)

Country Link
JP (1) JP2013098168A (en)
CN (2) CN103094030A (en)
DE (1) DE102012011309B4 (en)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
RU2731545C1 (en) * 2019-10-15 2020-09-04 Российская Федерация, от имени которой выступает Государственная корпорация по атомной энергии "Росатом" (Госкорпорация "Росатом") Method of generating x-rays for multi-frame pulse x-ray
RU2784895C1 (en) * 2022-04-26 2022-11-30 Федеральное государственное автономное образовательное учреждение высшего образования "Национальный исследовательский Томский политехнический университет" (ФГАОУ ВО НИ ТПУ) Source of bremsstrahlung

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102015217421B4 (en) 2015-09-11 2023-05-17 Siemens Healthcare Gmbh Spectral filtering of X-rays for energy-selective X-ray imaging
CN109961424B (en) * 2019-02-27 2021-04-13 北京大学 Hand X-ray image data generation method

Citations (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR997980A (en) * 1950-02-02 1952-01-14 Radiologie Cie Gle Strictly monochromatic and intense radiation crystallography tube
GB1247244A (en) * 1968-04-03 1971-09-22 Metallwerk Plansee Ag & Co K G Improvements in and relating to rotary targets for x-ray tubes
GB1262405A (en) * 1969-07-23 1972-02-02 Siemens Ag A rotary-anode x-ray tube
US4903287A (en) * 1987-05-18 1990-02-20 U.S. Philips Corporation Radiation source for generating essentially monochromatic x-rays
DE3940251A1 (en) * 1989-12-06 1991-06-13 Philips Patentverwaltung Focused hard X=ray source for imaging or analysis - has ring formed anode and elliptical surface of rotation multiple coated mirror to increase target energy density
CN2354503Y (en) * 1998-11-26 1999-12-22 西北核技术研究所 X-ray generator for mammography
CN1252618A (en) * 1998-10-22 2000-05-10 沈阳师范学院 Efficient X-ray machine with transmission anode
US6078644A (en) * 1998-07-01 2000-06-20 Varian Medical Systems, Inc. Carbon-backed x-ray target with coating
CN1287378A (en) * 2000-09-07 2001-03-14 清华大学 X-ray source of pyroelectric crystal
CN1453817A (en) * 2003-05-15 2003-11-05 谭大刚 Variable quasi-monoenergetic or bienergetic fluorescent X-ray source based on X-ray apparatus with transmission anode
US20040076260A1 (en) * 2002-01-31 2004-04-22 Charles Jr Harry K. X-ray source and method for more efficiently producing selectable x-ray frequencies
US20040264644A1 (en) * 2003-06-30 2004-12-30 Herbert Goebel System to generate therapeutic radiation
CN1574181A (en) * 2003-05-27 2005-02-02 通用电气公司 Axial flux motor driven anode target for x-ray tube
US20050123097A1 (en) * 2002-04-08 2005-06-09 Nanodynamics, Inc. High quantum energy efficiency X-ray tube and targets
CN101042976A (en) * 2007-03-27 2007-09-26 西北核技术研究所 Repeat frequency fast pulse hard x-ray generator
US7430276B2 (en) * 2004-02-25 2008-09-30 Nanodynamics-88 Low dose X-ray mammography method
CN101310359A (en) * 2006-02-01 2008-11-19 东芝电子管器件株式会社 X-ray source, and fluorescent x-ray analyzing device

Family Cites Families (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH02104564U (en) * 1989-02-07 1990-08-20
JP2962015B2 (en) * 1991-02-20 1999-10-12 松下電器産業株式会社 K-edge filter and X-ray device
JPH07243996A (en) * 1994-03-09 1995-09-19 Hitachi Ltd X-ray microanalysis method
DE19934987B4 (en) * 1999-07-26 2004-11-11 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. X-ray anode and its use
US6418193B1 (en) * 1999-11-01 2002-07-09 General Electric Company Imaging system including radiation filter for x-ray imaging
AU2003270505A1 (en) 2002-09-10 2004-04-30 Newton Scientific, Inc. X-ray feedback stabilization of an x-ray tube
DE102005026940A1 (en) * 2005-06-06 2006-12-14 Schering Ag X-ray arrangement for image presentation of an examination subject and use of the X-ray arrangement
US7203283B1 (en) 2006-02-21 2007-04-10 Oxford Instruments Analytical Oy X-ray tube of the end window type, and an X-ray fluorescence analyzer
WO2008078477A1 (en) * 2006-12-22 2008-07-03 Stanley Electric Co., Ltd. X-ray generating apparatus
JP2008268105A (en) * 2007-04-24 2008-11-06 Toshiba Corp X-ray beam source, x-ray beam irradiator, x-ray beam radiographic device, x-ray beam computer tomography device, x-ray element mapping examination apparatus and x-ray beam forming method

Patent Citations (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR997980A (en) * 1950-02-02 1952-01-14 Radiologie Cie Gle Strictly monochromatic and intense radiation crystallography tube
GB1247244A (en) * 1968-04-03 1971-09-22 Metallwerk Plansee Ag & Co K G Improvements in and relating to rotary targets for x-ray tubes
GB1262405A (en) * 1969-07-23 1972-02-02 Siemens Ag A rotary-anode x-ray tube
US4903287A (en) * 1987-05-18 1990-02-20 U.S. Philips Corporation Radiation source for generating essentially monochromatic x-rays
DE3940251A1 (en) * 1989-12-06 1991-06-13 Philips Patentverwaltung Focused hard X=ray source for imaging or analysis - has ring formed anode and elliptical surface of rotation multiple coated mirror to increase target energy density
US6078644A (en) * 1998-07-01 2000-06-20 Varian Medical Systems, Inc. Carbon-backed x-ray target with coating
CN1252618A (en) * 1998-10-22 2000-05-10 沈阳师范学院 Efficient X-ray machine with transmission anode
CN2354503Y (en) * 1998-11-26 1999-12-22 西北核技术研究所 X-ray generator for mammography
CN1287378A (en) * 2000-09-07 2001-03-14 清华大学 X-ray source of pyroelectric crystal
US20040076260A1 (en) * 2002-01-31 2004-04-22 Charles Jr Harry K. X-ray source and method for more efficiently producing selectable x-ray frequencies
US20050123097A1 (en) * 2002-04-08 2005-06-09 Nanodynamics, Inc. High quantum energy efficiency X-ray tube and targets
CN1453817A (en) * 2003-05-15 2003-11-05 谭大刚 Variable quasi-monoenergetic or bienergetic fluorescent X-ray source based on X-ray apparatus with transmission anode
CN1574181A (en) * 2003-05-27 2005-02-02 通用电气公司 Axial flux motor driven anode target for x-ray tube
US20040264644A1 (en) * 2003-06-30 2004-12-30 Herbert Goebel System to generate therapeutic radiation
US7430276B2 (en) * 2004-02-25 2008-09-30 Nanodynamics-88 Low dose X-ray mammography method
CN101310359A (en) * 2006-02-01 2008-11-19 东芝电子管器件株式会社 X-ray source, and fluorescent x-ray analyzing device
CN101042976A (en) * 2007-03-27 2007-09-26 西北核技术研究所 Repeat frequency fast pulse hard x-ray generator

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
王英华: "《X光衍射技术基础》", 30 April 1987, 原子能出版社 *

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
RU2731545C1 (en) * 2019-10-15 2020-09-04 Российская Федерация, от имени которой выступает Государственная корпорация по атомной энергии "Росатом" (Госкорпорация "Росатом") Method of generating x-rays for multi-frame pulse x-ray
RU2784895C1 (en) * 2022-04-26 2022-11-30 Федеральное государственное автономное образовательное учреждение высшего образования "Национальный исследовательский Томский политехнический университет" (ФГАОУ ВО НИ ТПУ) Source of bremsstrahlung

Also Published As

Publication number Publication date
CN108321070A (en) 2018-07-24
DE102012011309B4 (en) 2022-08-25
DE102012011309A1 (en) 2013-05-02
JP2013098168A (en) 2013-05-20

Similar Documents

Publication Publication Date Title
US11903754B2 (en) Monochromatic X-ray methods and apparatus
CN103119686B (en) Thick target for transmission X-ray pipe
US20240252836A1 (en) Monochromatic x-ray imaging systems and methods
US9036786B2 (en) Transmission type X-ray tube and reflection type X-ray tube
CN103094030A (en) Transmission type x-ray tube and reflection type x-ray tube
George et al. Energy-modulated x-ray fluorescence and luminescence emissions from therapeutic nanoparticles

Legal Events

Date Code Title Description
C06 Publication
PB01 Publication
C10 Entry into substantive examination
SE01 Entry into force of request for substantive examination
RJ01 Rejection of invention patent application after publication
RJ01 Rejection of invention patent application after publication

Application publication date: 20130508