WO2014172942A1 - Tube à rayons x basé sur l'émission de champ de nanomatériau lab6 et tomodensitomètre mobile - Google Patents

Tube à rayons x basé sur l'émission de champ de nanomatériau lab6 et tomodensitomètre mobile Download PDF

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Publication number
WO2014172942A1
WO2014172942A1 PCT/CN2013/076046 CN2013076046W WO2014172942A1 WO 2014172942 A1 WO2014172942 A1 WO 2014172942A1 CN 2013076046 W CN2013076046 W CN 2013076046W WO 2014172942 A1 WO2014172942 A1 WO 2014172942A1
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Prior art keywords
lab6
field emission
ray tube
anode
cathode
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PCT/CN2013/076046
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English (en)
Chinese (zh)
Inventor
徐如祥
林祖伦
代秋声
高枫
张涛
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中国人民解放军北京军区总医院
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Publication of WO2014172942A1 publication Critical patent/WO2014172942A1/fr

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    • 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
    • H01J35/06—Cathodes
    • H01J35/065—Field emission, photo emission or secondary emission cathodes

Definitions

  • the present invention claims the priority of a Chinese patent application filed on April 27, 2013, to the Chinese National Intellectual Property No. 201310151759.5, entitled "X-ray Tube and Mobile CT Scanner Based on LaB6 Nanomaterial Field Emission”.
  • the invention relates to the field of medical instruments, in particular to an X-ray tube and a mobile CT scanner based on field emission of lanthanum hexaboride (LaB6) nanomaterials.
  • LaB6 lanthanum hexaboride
  • the X-ray tube is a key component of a small medical CT device.
  • the cathode is the core component of the X-ray tube and directly determines the performance of the X-ray tube, the quality of the image such as resolution and contrast, and the efficiency of the whole machine.
  • the X-ray tube is usually an X-ray tube based on tungsten (W) wire thermal emission, that is, a cathode made of a tungsten (W) wire to form an X-ray tube, and the working principle is that the tungsten (W) wire is heated to its working temperature. When electrons are emitted, the electrons that are emitted by the heat bombard the anode, thereby generating X-rays.
  • W tungsten
  • the prior art X-ray tube based on tungsten (W) wire thermal emission has at least the following disadvantages:
  • the cathode in the existing X-ray tube adopts tungsten with high electron emission work ((
  • )w 4.52 eV), emission The current density is small.
  • the pure tungsten material has a thermal emission current density of only 0.3 A/cm 2 at 2200 ° C. If a larger total emission current is to be obtained, the cathode temperature is usually increased, but the cathode temperature is increased to cause the cathode material.
  • the evaporation rate increases, the evaporation of the cathode material causes the tungsten filament to become thinner, and the thinned tungsten cathode increases the cathode temperature and the cathode evaporation is intensified, thereby forming a vicious cycle; in addition, the evaporated tungsten cathode material is deposited on the On the shell, a continuous or intermittent tungsten conductive film is formed, which destroys the insulation strength of the X-ray tube, reduces the tube pressure, and the tube is scrapped, thereby reducing the life of the X-ray tube; at the same time, the tungsten conductive film blocks the output.
  • the X-ray intensity of the window reduces the imaging sensitivity.
  • the invention provides an X-ray tube and a mobile CT scanner based on LaB6 nanomaterial field emission, which is used for improving the overall performance of the X-ray tube, and can meet the application requirements of medical testing and the like.
  • the present invention provides an X-ray tube based on LaB6 nanomaterial field emission, comprising: an anode and a cathode; the cathode includes a LaB6 tip cone field emission array, and the field emission is generated by the external electric field Electrons bombard the anode to produce X-rays.
  • the invention also provides a mobile CT scanner comprising an X-ray tube based on LaB6 nanofield emission as described above.
  • the technical solution provided by the invention uses LaB6 nanomaterial as the tip material of the X-ray tube field emission cathode, and the LaB6 cusp field emission array thus obtained can generate a large amount of electrons generated by field emission under the electric field, thereby improving the beam current intensity.
  • the X-rays generated by the electron bombardment anode are very stable, which makes the X-rays generated by these electron bombardment anodes uniform, which is beneficial to improve the definition and resolution of X-ray imaging, reduce the radiation dose to the measured object, and facilitate the realization of X.
  • the miniaturization of the ray tube can meet the design requirements for miniaturization of portable devices such as mobile CT scanners and industrial inspection.
  • LaB6 nanomaterials have strong resistance to ion bombardment and high chemical stability, X-ray tubes based on LaB6 nanomaterial field emission have longer working life and more stable and reliable performance than other X-ray tubes.
  • FIG. 1 is a schematic structural view of an X-ray tube based on LaB6 nanomaterial field emission according to an embodiment of the present invention
  • 2A-2C are SEM photographs and field emission characteristics of an optional diode LaB6 cusp field emission array according to an embodiment of the present invention.
  • 3A-3C are SEM photographs and field emission characteristics of an optional triode LaB6 cusp field emission array according to an embodiment of the present invention.
  • FIG. 4 is a schematic structural diagram of another X-ray tube based on LaB6 nanomaterial field emission according to an embodiment of the present invention
  • FIG. 5 is an example of an X-ray tube anode model according to an embodiment of the present invention
  • FIG. 7 is a schematic structural diagram of another X-ray tube based on LaB6 nanomaterial field emission according to an embodiment of the present invention
  • FIG. 8 is a schematic diagram of an embodiment of the present invention.
  • An example of a relationship between an electron beam incident angle (or a target tilt angle) and a photon yield is provided.
  • FIG. 9 is a schematic diagram of an imaging principle of an X-ray tube in a medical examination such as a CT scan of a head according to an embodiment of the present invention
  • An example of a distribution curve of photon areal angles different from the target surface when the target surface angle is 5 degrees according to the embodiment of the present invention
  • FIG. 11 is perpendicular to the incident direction of the electron beam at different target tilt angles according to an embodiment of the present invention.
  • FIG. 12 is an example of a relationship between a target tilt angle and an X-photon number usable for imaging according to an embodiment of the present invention.
  • the elements in the figures are only shown for simplicity and clarity and are not necessarily drawn to scale. For example, the dimensions of some of the elements in the figures may be exaggerated relative to other elements in order to help improve the scope of the embodiments of the invention. - -
  • FIG. 1 is a schematic structural diagram of an X-ray tube based on LaB6 nanomaterial field emission according to an embodiment of the present invention.
  • the X-ray tube based on LaB6 nanomaterial field emission provided in this embodiment has a two-pole structure.
  • the X-ray tube comprises: an anode 1 and a cathode 2, the cathode 2 includes a LaB6 cone-cone field emission array, and the cathode 2 The electrons generated by the field emission under the action of the first electric field bombard the anode 1 to generate X-rays.
  • a cathode comprising a LaB6 tip cone field emission array made of one of LaB6 nanomaterials as a cathode material is a cold cathode relative to a prior art hot tungsten (W) filament cathode, including X-rays of the cold cathode
  • the principle of X-ray generation by the tube is as follows: LaB6 nanomaterial is used as the tip material of the cathode field emission. Under the action of the applied electric field, the field material emits electrons, and the electrons accelerate the bombardment of the anode under the high voltage electric field to generate X-rays.
  • LaB6 nanomaterials have the best physical and chemical properties and electron emission properties.
  • a large number of experimental results show that the LaB6 nanomaterials have a work function of 2.4-2.8 eV, which is much lower than that of a pure tungsten cathode of 4.52 eV. It has the advantages of strong anti-poisoning ability, strong anti-ion bombardment ability, stable chemical property and long service life, which can meet the material selection requirements of field emission cathode.
  • the LaB6 nanomaterial is used as the tip material of the X-ray field emission field (FEAs) cathode, and the LaB6 conical field emission array thus obtained can generate a large amount of electrons generated by field emission under the electric field, thereby improving
  • the intensity of the electron beam, the X-rays generated by the electron bombardment anode are very stable, so that the X-rays generated by these electron bombardment anodes are consistent, which is beneficial to improve the definition and resolution of X-ray imaging, and reduce the radiation dose to the measured object.
  • LaB6 cone field emission array in the X-ray tube is operated under vacuum, an absolute vacuum cannot be achieved in the X-ray tube and a small amount of air molecules are still present. After being ionized by the high-energy electron beam, these air molecules will accelerate toward the cathode under the strong electric field in the tube, and may bombard the cathode, thereby causing radiation damage of the cathode. Because LaB6 nanomaterials have strong resistance to ion bombardment and high chemical stability, X-ray tubes based on LaB6 nanomaterial field emission have longer working life and stable and reliable performance compared with other X-ray tubes.
  • the LaB6 cone field emission array comprises: a diode LaB6 cone field emission array, or a triode LaB6 cone field emission array. These LaB6 conical field emission arrays are easy to mass produce and cost less.
  • the diode LaB6 tip cone field emission array comprises: a silicon tip diode array and a LaB6 nano material film layer covering the surface of the silicon tip cone.
  • a Scanning Electron Microscope (SEM) image of an optional diode LaB6 tip cone field emission array is shown in Figure 2A and Figure 2B.
  • the field emission characteristics are shown in Figure 2C.
  • SEM Scanning Electron Microscope
  • the diode array as a field emission cone LaB6 cathode X-ray tube having a low threshold electric field, i.e., to achieve the required stability when the X-ray emission is small applied electric field, it can be an ordinary high vacuum ( ⁇ 10- 5 P a ) Long-term stable operation, it is easy to achieve high-frequency pulse emission of electron beam, fast response, long service life, and is beneficial to reduce power consumption, reduce radiation dose to the object under test, and have environmental protection and health benefits. Can better meet the practical needs of medical testing and other applications.
  • the triode LaB6 tip cone field emission array comprises: a silicon base, an array of cavities formed on the silicon base, an array of molybdenum tip cones distributed in each cavity, and a surface covering each molybdenum tip cone LaB6 nanomaterial film layer.
  • An SEM photograph of an optional triode LaB6 tip cone field emission array prepared by a conventional process such as the Spindt method is shown in Figure 3A.
  • An optional triode LaB6 tip prepared by mask oxidation technique (LOCOS method) is used.
  • the SEM photograph of the cone-field emission array is shown in Fig. 3B.
  • the field emission characteristics are shown in Fig. 3C.
  • the emission current density of the X-ray tube is 0.6 A/cm 2 , which is equivalent to the average emission current of the single-point ⁇ . 0.24 ⁇ .
  • the X-ray tube using the triode LaB6 cone-cone field emission array as the cathode has a low field emission on-field strength and a high field emission current density, and can be stably stabilized under ordinary high vacuum ( ⁇ 10- 5 Pa).
  • the X-ray tube based on the LaB6 nanomaterial field emission provided in this embodiment has a three-pole structure. As shown in FIG. 4, the X-ray tube includes: an anode 1, a cathode 2, and a gate disposed between the anode 1 and the cathode 2. 3. Applying a first electric field between the cathode 2 and the gate 3 to cause the cathode field emission to generate electrons, and applying a second electric field between the gate 3 and the anode 1 to accelerate electrons passing through the gate 3 to bombard the anode 1 to generate X-rays.
  • the X-ray tube based on LaB6 nanomaterial field emission provided in this embodiment has a gate between the anode and the cathode. Due to the protection of the grid, most of the air ions cannot directly hit the cathode, thereby reducing the radiation damage of the cathode. Probability; In addition, through the voltage control applied to the gate, the on or off control of the cone emission can also be realized, and the pulse emission of the electron beam can be easily realized, and the response speed is fast and the service life is long. When working with pulse exposure imaging mode, the number of projection angles and radiation dose of the sample can be significantly reduced, and the rotation artifact can be effectively suppressed, thereby better meeting the practical application requirements such as medical detection.
  • the gate may be a metal mesh gate made of a metal mesh.
  • the anode 1 includes an anode body 11 and a target surface 12 disposed on the anode body 11.
  • the anode material By reasonably selecting the anode material, the maximum beam intensity that it is subjected to can be effectively increased.
  • the anode body is a copper anode body
  • the target surface is a tungsten alloy target surface.
  • electrons emitted from the cathode are accelerated by an electric field and then impinged on the anode target to generate X-rays, wherein more than 99% of the energy of the electron beam is converted into heat deposited in the anode, and less than about 1% of the energy is converted into X. Rays.
  • the X-ray tube can be designed using a fixed anode scheme, that is, the anode in the X-ray tube based on LaB6 nanomaterial field emission is a fixed anode. The advantage of this solution is to effectively reduce the weight and volume of the X-ray source and to reduce the difficulty in manufacturing and using the X-ray tube.
  • tungsten has a high melting point but poor thermal conductivity; copper has good thermal conductivity but low melting point. Although graphite has higher melting point and specific heat than tungsten and copper, its atomic number is low and X-ray generation efficiency is low. Therefore, copper can be used as the anode body to take advantage of its good thermal conductivity, and a tungsten alloy sheet is used as a target surface to utilize its high melting point performance. Due to the inconsistent properties of copper and tungsten, the thickness of the tungsten alloy sheet is a key parameter for anode design.
  • the thickness of the tungsten alloy sheet needs to be selected to an optimum value.
  • thermal analysis software can be used to simulate the temperature rise curve of the tungsten alloy sheet with different thicknesses under different electron beam pulse bombardment, tungsten alloy sheet and adjacent metal copper, and heat at the anode. In the transfer process, the relationship between material thickness, electron beam intensity and temperature is studied.
  • the physical model of the anode is shown in Figure 5:
  • the copper anode body has a geometry of 040x50mm, the target surface material is tungsten, the tungsten alloy sheet has a diameter of 01Omm, the focal diameter is 01mm, and the thickness of the tungsten alloy sheet ranges from 20 ⁇ to 2 ⁇ , X.
  • the tube voltage is 140kV and the current range is 2mA ⁇ 10mA.
  • the ANSYS12 can be used to establish an X-ray tube anode finite element model for thermal analysis calculations.
  • the temperature distribution on the anode can be calculated by changing the thickness and current intensity of the tungsten alloy sheet.
  • the electron beam is struck on the surface of tungsten with a focal diameter of 01 mm.
  • the average depth of electrons entering the surface of tungsten is 5 ⁇ m.
  • the electrons generate heat within this tiny volume.
  • One is a simplified method of applying a load, applying a load to the surface, that is, at the center of tungsten. - -
  • a thermal load is applied to the surface of 01, and the amount of heat flow applied to the surface can be calculated according to the voltage and current; the other method is to apply a load to the actual situation, and apply a thermal load to the body, that is, a cylinder of 01x0.005 mm. on.
  • the heat transfer rate is proportional to the area.
  • 100 is the radiation force, the unit is W/m 2 ; s is the emissivity of the object; c is the black body emissivity, 5.67W / (m 2 'K 4 ); - -
  • ⁇ is the surface temperature of the object.
  • the following is a simulation result that ignores the radiation heat dissipation and the conduction heat dissipation of the insulating oil.
  • the maximum time for completing a CT scan is 30s, so the X-ray tube must be able to work continuously for 30s during scanning.
  • the optimal tungsten alloy sheet thickness and the maximum constant current that can be tolerated are calculated. value. It can be seen from Fig. 6 that in the case of continuous incident electrons, when the thickness of the tungsten alloy sheet is 400 to 500 ⁇ m, the maximum withstand current is 7.5 mA. On the left side of the highest point of the curve in the figure, the copper will melt first, and on the right, the tungsten alloy sheet will melt first. For the pulse mode of operation, the maximum pulse current that a tungsten alloy sheet of the same thickness can withstand at different duty cycles increases as the duty cycle decreases.
  • the embodiment of the present invention will select a tungsten alloy target surface having a thickness of 400-500 um, for example, preferably 0.5 mm, as a preferred thickness value of the tungsten alloy sheet.
  • the anode 10 of the X-ray tube includes an anode body 101 and a target surface 102.
  • the target surface 102 is formed with a predetermined target plane tilt angle ⁇ with respect to the reference direction, and the reference direction is perpendicular to the electron incident direction, as shown in FIG.
  • the target tilt angle ⁇ is a key parameter that directly affects the light yield, effective focus size, heat distribution and transfer of the X-ray tube.
  • Monte Carlo method can be used to simulate the calculation.
  • EGS software was used to simulate lxlO 7 140keV electrons bombarding tungsten targets with different dip angles, and the spatial distribution of light yield and photons was counted.
  • the relationship between the target tilt angle and the photon yield is shown in Fig. 8.
  • the smaller the target tilt angle the higher the X-photon yield.
  • - - the smaller the target angle, the better, which requires careful analysis.
  • the X-ray photons in the fan beam which are approximately perpendicular to the incident direction of the electron beam are used.
  • This part of the X-ray photo is actually contributing to the CT mission (as shown in Fig. 9), so this angle range The more X-rays inside, the better.
  • the figure below shows the photon areal density at an angle different from the target surface at a target angle of 5 degrees.
  • the areal density of photons becomes smaller and smaller, and the number of X-photons that can be used for imaging becomes less and less. Therefore, although the total photon yield at a target angle of 5 degrees is high, the photon surface density at an angle of 85 degrees from the target surface is low.
  • the number of X-photons in the exit plane perpendicular to the incident direction of the electron beam at different target inclination angles is counted.
  • the statistical results are shown in Fig. 11. As can be seen from Fig. 11, as the target tilt angle increases, the number of photons on the exit surface increases, but reaches a maximum at about 45 degrees and then begins to decrease.
  • the resolution of the tomographic image is the effective focus of the X-ray tube, not the actual focus.
  • the relationship between the actual focus size L and the projected effective focus size d is as follows:
  • the size d of the effective focus can be controlled by reducing the target tilt angle ⁇ . If the density of the cross-sectional area of the incident electron beam cannot be increased, it can be seen from the following equation that increasing the electron beam width h by decreasing the target tilt angle ⁇ may increase the total number of imageable X-photons.
  • the target tilt angle is preferably 11 degrees.
  • the total length of the X-ray tube in the above embodiment is less than or equal to 120 mm, so as to fully ensure the compact shape of the X-ray tube, which can be easily carried, and is convenient for special environments such as shipboard, vehicle, and battlefield hospitals.
  • the maximum diameter in the above embodiment is less than or equal to 60 mm.
  • the distance between the anode and the tip of the tip of the cathode in the above embodiment is less than or equal to 10 um. This ensures excellent performance of the X-ray tube.
  • the present invention also provides a mobile CT scanner comprising the X-ray tube based on LaB6 nanomaterial field emission provided by any of the above embodiments, through which X-rays are generated to the brain Wait for the body part to be medically tested.
  • the foregoing program may be stored in a computer readable storage medium, and the program is executed when executed.
  • the foregoing storage device includes the following steps:
  • the foregoing storage medium includes: a Read-Only Memory (ROM), a Random Access Memory (RAM), a magnetic disk, or an optical disk.
  • ROM Read-Only Memory
  • RAM Random Access Memory

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Abstract

L'invention concerne un tube à rayons X basé sur l'émission de champ de nanomatériau LaB6 et un tomodensitomètre mobile. Le tube à rayons X comprend une anode (1) et une cathode (2). La cathode (2) comprend une matrice d'émission de champ conique aigu au LaB6, et des électrons générés par l'émission de champ de la cathode (2) sous l'effet d'un champ électrique externe bombardent l'anode (1) pour générer un rayon X. Une grille (3) peut aussi être disposée entre l'anode (1) et la cathode (2). Le tube à rayons X améliore l'intensité d'un courant de faisceau d'électrons, génère un rayon X stable et fiable, et a une grande longévité ; et le tube à rayons X aide à améliorer la définition et la résolution d'imagerie à rayons X et à réduire la dose de rayonnement vers un objet détecté, facilite la miniaturisation du tube à rayons X et peut répondre aux besoins de miniaturisation relatifs à la conception de dispositifs portatifs, par exemple un tomodensitomètre mobile.
PCT/CN2013/076046 2013-04-27 2013-05-22 Tube à rayons x basé sur l'émission de champ de nanomatériau lab6 et tomodensitomètre mobile WO2014172942A1 (fr)

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CN201310151759.5A CN103337441B (zh) 2013-04-27 2013-04-27 基于LaB6纳米材料场发射的X射线管及移动CT扫描仪
CN201310151759.5 2013-04-27

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CN103337443B (zh) * 2013-04-27 2016-05-18 中国人民解放军北京军区总医院 医学检测用x射线源及移动ct扫描仪
CN103340641B (zh) * 2013-04-27 2016-06-08 中国人民解放军北京军区总医院 Ct扫描仪脉冲成像系统及其脉冲成像方法
CN103731966B (zh) * 2014-01-03 2015-12-30 中国原子能科学研究院 一体化荧光发生装置
EP3742468A1 (fr) * 2019-05-20 2020-11-25 Siemens Healthcare GmbH Modulation de dose

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN1069438C (zh) * 1994-10-28 2001-08-08 株式会社岛津制作所 X射线管阳极及其制造方法与静止阳极x射线管
US20020053869A1 (en) * 1998-08-26 2002-05-09 Ahn Kie Y. Field emission display having reduced power requirements and method
CN1479935A (zh) * 2000-10-06 2004-03-03 北卡罗来纳-查佩尔山大学 使用电子场发射阴极的x-射线发生机构
CN101097823B (zh) * 2006-06-30 2011-01-05 鸿富锦精密工业（深圳）有限公司 微型场发射电子器件
CN102988076A (zh) * 2012-12-11 2013-03-27 苏州生物医学工程技术研究所 Ct扫描仪

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN1145914C (zh) * 1996-07-08 2004-04-14 三星电管株式会社 场致发射显示装置
CN201936839U (zh) * 2011-01-10 2011-08-17 深圳市晶金电子有限公司 照相设备及其x射线发生器

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN1069438C (zh) * 1994-10-28 2001-08-08 株式会社岛津制作所 X射线管阳极及其制造方法与静止阳极x射线管
US20020053869A1 (en) * 1998-08-26 2002-05-09 Ahn Kie Y. Field emission display having reduced power requirements and method
CN1479935A (zh) * 2000-10-06 2004-03-03 北卡罗来纳-查佩尔山大学 使用电子场发射阴极的x-射线发生机构
CN101097823B (zh) * 2006-06-30 2011-01-05 鸿富锦精密工业（深圳）有限公司 微型场发射电子器件
CN102988076A (zh) * 2012-12-11 2013-03-27 苏州生物医学工程技术研究所 Ct扫描仪

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