NZ753547B2 - X-ray source - Google Patents

X-ray source Download PDF

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Publication number
NZ753547B2
NZ753547B2 NZ753547A NZ75354716A NZ753547B2 NZ 753547 B2 NZ753547 B2 NZ 753547B2 NZ 753547 A NZ753547 A NZ 753547A NZ 75354716 A NZ75354716 A NZ 75354716A NZ 753547 B2 NZ753547 B2 NZ 753547B2
Authority
NZ
New Zealand
Prior art keywords
ray
distributed
portable
ray source
array
Prior art date
Application number
NZ753547A
Other versions
NZ753547A (en
Inventor
Paul Betteridge
Mark Evans
Martin Holden
Abdul Sami Mughal
Kristen Schmiedehausen
Gil Travish
Original Assignee
Adaptix Ltd
Filing date
Publication date
Application filed by Adaptix Ltd filed Critical Adaptix Ltd
Priority claimed from PCT/GB2016/053259 external-priority patent/WO2018073554A1/en
Publication of NZ753547A publication Critical patent/NZ753547A/en
Publication of NZ753547B2 publication Critical patent/NZ753547B2/en

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Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/02Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/025Tomosynthesis
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/40Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4007Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units
    • A61B6/51
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/56Details of data transmission or power supply, e.g. use of slip rings
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/58Testing, adjusting or calibrating apparatus or devices for radiation diagnosis
    • A61B6/587Alignment of source unit to detector unit
    • HELECTRICITY
    • H01ELECTRIC ELEMENTS
    • H01JELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J2235/00X-ray tubes
    • H01J2235/06Cathode assembly
    • H01J2235/068Multi-cathode assembly
    • HELECTRICITY
    • H01ELECTRIC ELEMENTS
    • H01JELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00X-ray tubes
    • H01J35/02Details
    • H01J35/04Electrodes ; Mutual position thereof; Constructional adaptations therefor
    • H01J35/06Cathodes
    • H01J35/065Field emission, photo emission or secondary emission cathodes
    • HELECTRICITY
    • H01ELECTRIC ELEMENTS
    • H01JELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J35/00X-ray tubes
    • H01J35/02Details
    • H01J35/14Arrangements for concentrating, focusing, or directing the cathode ray

Abstract

portable x-ray source (100) is provided that enables a faster turn on time through the use of emission controls (110) capable of preventing emitted electrons from striking targets comprised of a material effective at high-energy bremsstrahlung. The portable x ray source (100) comprises: a distributed x-ray generator array (103); a means of producing high voltages (109); and a means for collimating x-rays emitted by the generator array. The distributed x-ray generator array comprises: a plurality of electron field emitters (104); a plurality of targets (106) each capable of emitting x-ray photons, and wherein each target is positioned out of alignment with a straight axis from each electron field emitter along which electrons emitted by each electron field emitter travel; a means of withstanding high-voltage between the electron field emitters and the targets; a means of spacing the electron field emitters from the targets (108); a means of selectively controlling the emission of x-rays from the distributed x-ray generator array (110); an enclosure (101) wherein said plurality of electron field emitters and plurality of targets are maintained in a vacuum; and a means of filtering low-energy x-ray photons.

Description

A le x-ray source (100) is provided that enables a faster turn on time through the use of emission controls (110) capable of preventing emitted electrons from striking targets comprised of a material effective at high-energy trahlung. The portable x ray source (100) comprises: a distributed x-ray generator array (103); a means of producing high voltages (109); and a means for collimating x-rays emitted by the generator array. The distributed x-ray generator array comprises: a ity of electron field emitters (104); a plurality of s (106) each capable of emitting x-ray photons, and wherein each target is positioned out of alignment with a straight axis from each electron field emitter along which electrons emitted by each electron field emitter travel; a means of withstanding high-voltage between the electron field emitters and the s; a means of spacing the electron field emitters from the s (108); a means of selectively controlling the emission of x-rays from the distributed x-ray tor array (110); an enclosure (101) wherein said plurality of electron field emitters and plurality of targets are maintained in a vacuum; and a means of filtering low-energy x-ray photons.
NZ 753547 Description Title of Invention: X-RAY SOURCE The present invention generally relates to an x—ray g source, and more par— ticularly, to a portable x—ray imaging source capable of motion-free, tomosynthesis g, and suitable for dental and small body-part/small area imaging.
Conventional x-ray imaging is commonly based on planar radiography. This approach utilizes a single, high-power point-like x—ray source made up of a set of vacuum—tubes capable of generating a single cone or fan beam of x-rays over a wide range of energies and ts.
Such s typically require the x-ray source be placed a significant distance from the person to be imaged to ensure the x—ray covers a sufficient area, and to maintain a "skin safe distance" — the m distance necessary to avoid an excessive x-ray dose at a particular entry point on the skin. This large stand-off distance, or distance between the source and object, necessitates a lot of power. To provide this power, con- ventional x-ray systems use large, expensive, and heavy (in the tens of kilograms), power supplies. Such power supplies often require cooling, which further adds to the bulk, weight, and cost of the system. The end result is that such conventional systems are typically fixed (not portable) or otherwise occupy a large space, and impose a high capital cost on end users, such as hospitals, y care facilities, screening clinics, and dental offices.
In addition, such conventional, single-source systems (absent a gantry or other means of moving the source) are generally only capable of generating two-dimensional (2D) . Conventional two-dimensional (or planar) imaging is often inadequate for fying es (or biomarkers) ial for clinical detection and diagnostics.
This is particularly true in dental and small-body part/small—area imaging, such as mammography.
In dental diagnostics, intraoral (taken inside the mouth) x-rays or radiographs are the most common images used to diagnose dental problems. But because intraoral ra— diographs are two-dimensional, they often prove to be inadequate for identifying a wide host of clinical issues, including vertical root fractures, bone loss, implant in- stability; and dental caries (tooth decay) — the latter of which is the most prevalent c disease in both children and adults, e being largely preventable. One particular challenge to dentists is ming a nerve canal’s position relative to the root prior to molar extraction. Currently the best devices for such a procedure are Cone Beam Computed Tomography (CBCT) systems. But due to the high radiation exposure inherent to CBCT, typically 30—150x that of planar dental imaging, the use of CBCT is generally avoided, especially in cases where the danger posed by the condition is not ?????????????????????????????? ???????????????????????????????????? ?M?;?9?F?;?6?+?)?F?N?X?-?F?G?P?9?:?X?N?G?X?C?-?J?;?N?X?M?P?+?:?X?-?T?H?G?M?P?J?-???X???A?M?G???X?,?P?-?X?N?G?X?N?:?-?X?+?G?M?N?X?G?/?X???????%?X?-?I?P?;?H?C?-?F?N?X ?C?)?F?U?X?,?-?F?N?;?M?N?M?X?,?G?X?F?G?N?X?:?)?Q?-?X?)?+?+?-?M?M?X?N?G?X?M?P?+?:?X?M?U?M?N?-?C?M???X?%?:?-?J?-?7?J?-???X?,?-?F?N?;?M?N?M?X?)?J?-?X?8?-?I?P?-?F?N?A?U?X ?P?;?J?-?,?X?N?G?X?H?J?G?+?-?-?,?X???G?F?X?J?;?M?@???X?S?;?N?:?X?A?;?C?;?N?-?,?X?;?F?7?J?C?)?N?;?G?F?X?8?G?C?X?N?S?G???,?;?C?-?F?M?;?G?F?)?A???X?H?A?)?F?)?J?X?T?W ?J?)?U?X?;?C?)?9?-?M?X?)?M?X?9?P?;?,?)?F?+?-???X ?’?????????(?X?$?;?C?;?A?)?J?X?;?M?M?P?-?M?X?)?J?;?M?-?X?;?F?X?G?N?:?-?J?X?M?C?)?A?A???)?J?-?)?X?;?C?)?9?;?F?9?X?)?H?H?A?;?+?)?N?;?G?F?M???X???G?J?X?-?T?)?C?H?A?-???X?C?)?C?W ?J?)?H?:?U?X?;?M?X?)?X?M?H?-?+?;?)?A?;?V?-?,?X?C?-?,?;?+?)?A?X?;?C?)?9?;?F?9?X?N?-?+?:?F?;?I?P?-?X?N?:?)?N?X?P?M?-?M?X?T???J?)?U?M?X?N?G?X?M?-?-?X?;?F?M?;?,?-?X?N?:?-?X ?*?J?-?)?M?N?M???X?)?F?,?X?;?M?X?)?F?X?-?M?M?-?F?N?;?)?A?X?C?-?,?;?+?)?A?X?,?;?)?9?F?G?M?N?;?+?X?N?G?G?A?X?;?F?X?N?:?-?X?-?)?J?A?U?X?,?-?N?-?+?N?;?G?F?X?G?/?X?*?J?-?)?M?N?X ?,?;?M?-?)?M?-?M???X???P?N?X?N?S?G???,?;?C?-?F?M?;?G?F?)?A?X?C?)?E?C?G?9?J?)?H?:?U?X?;?M?X?9?-?F?-?J?)?A?A?U?X?A?-?M?M?X?-?5?+?)?+?;?G?P?M?X?O?:?)?F?X?,?;?9?;?N?)?A?X ?*?J?-?)?M?N?X?N?G?C?G?M?U?F?N?:?-?M?;?M???X?G?J?X?N?:?J?-?-???,?;?C?-?F?M?;?G?F?)?A?X?????????X?C?)?C?C?G?9?J?)?H?:?U???X???F?X?,?;?9?;?N?)?A?X?*?J?-?)?M?N?X?N?G?W ?C?G?M?U?F?N?:?-?M?;?M?X?C?P?A?N?;?H?A?-?X?;?C?)?9?-?M?X?G?/?X?N?:?-?X?*?J?-?)?M?N???X?)?N?X?,?;?2?-?J?-?F?N?X?)?F?9?A?-?M???X?)?J?-?X?+?)?H?N?P?J?-?,?X?)?F?,?X?J?-?+?G?F?W ?M?N?J?P?+?N?-?,?X?G?J?X???M?U?F?N?:?-?M?;?V?-?,???X?;?F?X?)?X?N?:?J?-?-???,?;?C?-?F?M?;?G?F?)?A?X?;?C?)?9?-?X?M?-?N???X???P?L?-?F?N?A?U?X?*?J?-?)?M?O?X?N?G?W ?C?G?M?U?F?N?:?-?M?;?M?X?J?-?I?P?=?J?-?M?X?C?G?Q?;?F?9?X?N?:?-?X?T???J?)?U?X?M?G?P?J?+?-?X?;?F?X?)?F?X?)?J?+?X?)?F?,?X?M?N?G?H?H?;?F?9?X?)?N?X?C?P?B?N?;?H?A?-?X?H?G?;?F?N?M???X ?N?:?P?M?X?)?,?,?;?F?9?X?N?G?X?N?:?-?X?+?G?M?N?X?)?F?,?X?N?G?N?)?A?X?;?C?)?9?;?F?9?X?N?;?C?-?X?,?P?J?;?F?9?X?S?:?;?+?:?X?N?:?-?X?*?J?-?)?M?N?X?;?M?X?:?-?A?,?X?;?F?X?)?X?+?G?C?W ?H?J?-?M?M?;?F?9?X?+?A?)?C?H???X?A?-?)?,?;?F?9?X?N?G?X?H?)?N?;?-?F?N?X?,?;?M?+?G?C?7?J?N???X ?’?????????(?X?"?G?H?P?A?)?N?;?G?F?X?M?N?P?,?;?-?M?X?M?:?G?S?X?N?:?)?N?X?M?+?J?-?-?F?;?F?9?X?S?;?N?:?X?*?J?-?)?M?N?X?N?G?C?G?M?U?F?N?:?-?M?;?M?X?J?-?M?P?A?N?M?X? 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cilities, and dental offices, who are often required to make large capital investments in g systems, and thus may increase the availability of three-dimensional x-ray imaging. For example, deploying a portable three-dimensional x-ray imaging source within a multi-dentist practice would be ormative given that due to equipment cost many dentists do not have access to CBCT or other three-dimensional g systems, and thus are often forced to rely on limited two-dimensional planar x-ray images.
The shorter off distances achievable by embodiments of the present disclosure also enable a reduction of radiation r (side scatter and backscatter), which in turn reduces the risk of x-ray exposure for x-ray operators and clinical workers. r radiation may be further reduced by use of a gross collimator 115, which may absorb x-rays that are not useful for imaging purposes, such as x-rays outside the region of interest of object (ROI) 203, while allowing x-rays useful to imaging to strike the ROI.
Gross collimator 115 may comprise a structure made of x-ray attenuating materials (e.g., high-density material(s) with high x-ray absorption). In one aspect, gross collimator 115 may comprise an elevated plane (or walls) that limits the area illuminated by portable x-ray source 100 to a ROI. In this way, gross collimator 115 may reduce non-imaging dosages of x-ray photons by lessening, if not removing, x-ray backscatter and side-scatter. Thus, gross ator 115 may serve to minimize unnecessary , and potentially harmful radiation exposure, without impacting x-ray image quality.
The use of such a gross collimator 115 is particularly useful for imaging where the te area of the detectors is small, and in cases where sensitive organs are adjacent to the area to be imaged. An example of such a use case is dental imaging: the intraoral ors are often 2cm x 4cm or smaller and the teeth and jaws of interest lie in close proximity to the brain.
Referring back to Figure 1, distributed x-ray generator array 103 may comprise a plurality of electron field emitters 104 aligned or otherwise paired with a plurality of targets 106. In this way, each generator 102 may be comprised of an electron field r 104 paired with a target 106. Each on field emitter 104 may be capable of generating a beam of electrons that may be ed at a target 106, such as a material effective at high-energy bremsstrahlung, to produce x-rays.
The plurality of electron field emitters 104 (and thus the plurality of targets 106) may be arranged as an emitter array 105. Emitter array 105 may comprise any of several configurations, including a two-dimensional array forming a square grid; a triangular grid also known as a "hexagon pack," or electron field emitters 104 may be randomly spaced. 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?4?!?$?;?G???.? ???G?4? ?E?G?.?6?A?>?$?G?$?2?$?"???;?6?5?G ?’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power supply 109 may produce positive voltages, and in a further aspect, may operate at a fixed voltage between 0kV. In yet another aspect of the present disclosure, power supply 109 may be capable of operating at two or more voltages, sequentially or in parallel.
High-voltage, power es (e.g., -30kV to -80kV), as described in the present disclosure, run contrary to conventional x-ray imaging approaches. In particular, conventional approaches teach that electron field emitters are to be driven by low- to moderate- power supplies, and teach away from use of high-voltage power supplies 109. Conventional approaches also teach away from compact power supplies, where the gap between the ground and high-tension plane is minimized.
As illustrated in Figure 1, the geometry of high-voltage power supply 109 may generally follow that of electron field emitters 104 and targets 106, and the output plane of high-voltage power supply 109 may touch electron field emitters 104 to form an electrical contact. In an aspect of the present disclosure le for dental radiology, high-voltage power supply 109 may be 30mm thick with a transverse size of 150mm by 150mm. Portable, x-ray source 100 may be packaged in liquid (insulating oils) and/or solid (putty, potting), so as to provide the insulation ed for the highvoltage of high-voltage power supply 109.
In another embodiment (not illustrated), distributed x-ray generator array 103 may be powered by a plurality of ferroelectric ls as described in .
Alternatively, as would be understood by a person of skill in view of the present disclosure, distributed x-ray tor array 103 may be powered by any number of s capable of producing the desired voltage.
Portable x-ray source 100 may further include a plurality of emission ls 110.
The ity of emission controls 110 may be capable of lling (e.g., defocusing/ focusing or deflecting/steering) electrons emitted by electron field emitters 104. In this way, emission control 110 may be capable of regulating the emission of x-rays by each generator 102. In turn, this enables each tor 102 to be dually addressable (controllable) and thus enables distributed x-ray generator array 103 to te temporally-separated, but physically overlapping x-ray conelets. This allows for seamless coverage of an object to be imaged, and maximal use of the available flux while maintaining the ability to have minimal stand-off distances.
The plurality of emission controls 110 may be capable of defocusing/focusing or ting /steering electron beams from an electron field emitter 104, individually onto or away from target 106, and thus may affect the production or cessation of x-rays respectively.
It will be appreciated by one skilled in the art that emission control is not limited to one approach, and may be used in combination with one or more s, including through electro-static, magneto-static and electro-magnetic means. One such approach is described in 2015/050639.
Figure 3 shows an example of a plurality of emission controls 110 comprising a plurality of selectively-powered coils or magnets (coils/magnets) 301. Coils/magnets 301 may be capable of preventing electron beams 304 d by an electron field emitter 104 from striking a portion of a target 106 comprised of a material ive at high-energy bremsstrahlung, and thus may be capable of controlling x-ray emission.
As illustrated in Figure 3, the output flux ron beam 304) of on field emitter 104 may be controlled by using electromagnetic fields generated by coils/ magnets 301 such that when energized or "on" 302 the fields produced deflect the electron beam 304 away from the ballistic trajectory/axis 307 and onto target 106.
When coils/magnets 301 are "off' 303, the electron beam 304 continues directly on axis 307 and s substrate 305, which may be comprised of low atomic number materials which only tes low energy photons that produce no signal. Thus, the state of magnets 301 (on 302 or off 303) serves as a control of the generation of x-rays 306 from a given emitter.
In an aspect of the present disclosure, target 106 may comprise a discrete area made of an effective trahlung material, such as tungsten, an nt area made of a low-Z material, such as silicon, and a support made of a conductive material, such as aluminum. Lenses or yokes maybe used to elongate the magnetic field in the beam axis direction, and t it off axis.
In a further embodiment of the t disclosure, the individual selectively-powered coils/magnets 301 may be arranged in clusters of coils/magnets in a pattern essentially equivalent to that of emitter array 105. The clusters may comprise four magnets 301 capable of creating a dipole magnetic field arranged about each electron field emitter 104. Alternatively, the clusters may comprise eight or more coils/magnets 301 ed such that a central set of coils creates a dipole field for ting the beam trajectory of the electron field emitter 104 and surrounding coils/magnets 301 are used to offset the stray field of the central coils/magnets 301, these clusters being configured in a pattern essentially equivalent to that of emitter array 105.
In aspects of the present disclosure, it may be necessary for solenoid coil 301 to deflect the electron beam a distance of 0.1 mm to 1.25 mm from the nominal path. describes methods of achieving such deflection using highcurrent coils. Notably, using clusters of coils, as described herein, similar results may be achieved at low currents.
Portable x-ray source 100 may also include a mechanism capable of selectively controlling x-ray emission from distributed x-ray generator array 103. In an aspect of the present disclosure, said mechanism may comprise a circuit(s), such as an addressing and timing circuit(s), capable of selectively activating one or more controller 110, such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Claims (14)

1. A portable x-ray source, sing: a distributed x-ray generator array; a means of producing high voltages, wherein said high voltages are e of powering the distributed x-ray generator array; and a means for collimating x-rays emitted by the distributed x-ray generator array to be within an area at a given distance; wherein the distributed x-ray tor array comprises: a plurality of electron field emitters; a plurality of targets, wherein each target is capable of ng x-ray photons when electrons are incident upon an area of said target comprised of a material effective at high-energy bremsstrahlung, and wherein each target is positioned out of alignment with a ht axis from each electron field emitter along which electrons emitted by each electron field emitter travel; a means of withstanding high-voltage between the electron field emitters and the targets; a means of spacing the electron field emitters from the targets; a means of ively controlling the emission of x-rays from the distributed x-ray generator array comprising a plurality of emission controls capable of controlling electrons d by the electron field rs to strike the area of said targets comprised of a material effective at high-energy bremsstrahlung; an enclosure n said plurality of electron field emitters and plurality of targets are maintained in a vacuum; and a means of filtering low-energy x-ray s.
2. The portable x-ray source of claim 1, wherein the distributed x-ray generator array further comprises a plurality of gates, wherein each gate is capable of controlling the emission field of an associated electron field emitter.
3. The portable x-ray source of claim 2, wherein the distributed x-ray generator array further comprises; a means of spacing the gates from the on field emitters; a means of powering the gates; and a means of spacing the gates from the targets.
4. The portable x-ray source of claim 1, wherein the distributed x-ray generator array r comprises a ator array comprised of a plurality of collimators, wherein each ator is capable of narrowing the angle of x-rays emitted by an associated target.
5. The x-ray source of claim 1, wherein the distributed x-ray tor array further comprises a fixed array.
6. The portable x-ray source of claim 1, wherein the distributed x-ray generator array further comprises a planar array.
7. The portable x-ray source of claim 1, wherein the plurality of emission controls comprises one of a plurality of electromagnetic coils or a plurality of parallel-plate deflectors.
8. The portable x-ray source of claim 1, further comprising a housing; wherein said housing comprises an inner enclosure which isolates high-voltage components of the portable x-ray source, and an outer enclosure which contains other ents of the portable x-ray .
9. The portable x-ray source of claim 1, r comprising one or more sensors, wherein said one or more sensors enable the distributed x-ray generator array to be aligned to an x-ray detector without requiring contact between the buted x-ray generator array and the x-ray detector.
10. The le x-ray source of claim 1, wherein the means of producing high voltages is capable of converting battery voltage to said high voltages for powering the distributed x-ray generator array without reliance on external power.
11. The portable x-ray source of claim 1, wherein the means of producing high voltages is capable of converting line voltage to said high es for powering the distributed x-ray generator array.
12. The portable x-ray source of claim 1, wherein the means of producing high voltages is capable of producing voltage in the range of -30kV to -80kV , or is capable of operating at ntially one fixed voltage.
13. The portable x-ray source of claim 1, wherein the means of selectively controlling the emission of x-rays from the distributed x-ray tor array comprises a digital addressing and timing circuit.
14. The portable x-ray source of claim 1, wherein the distributed x-ray generator array has a te pitch spacing in the millimeter to centimeter range. ?????????????????????????????? ???????????????????????????????????? ????????????????
NZ753547A 2016-10-19 X-ray source NZ753547B2 (en)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/GB2016/053259 WO2018073554A1 (en) 2016-10-19 2016-10-19 X-ray source

Publications (2)

Publication Number Publication Date
NZ753547A NZ753547A (en) 2023-08-25
NZ753547B2 true NZ753547B2 (en) 2023-11-28

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