EP2215498A2 - Système d'imagerie à énergie dirigée - Google Patents

Système d'imagerie à énergie dirigée

Info

Publication number
EP2215498A2
EP2215498A2 EP08852590A EP08852590A EP2215498A2 EP 2215498 A2 EP2215498 A2 EP 2215498A2 EP 08852590 A EP08852590 A EP 08852590A EP 08852590 A EP08852590 A EP 08852590A EP 2215498 A2 EP2215498 A2 EP 2215498A2
Authority
EP
European Patent Office
Prior art keywords
imaging system
particles
signal
charge
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.)
Withdrawn
Application number
EP08852590A
Other languages
German (de)
English (en)
Other versions
EP2215498A4 (fr
Inventor
James Cornwell
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.)
Kaonetics Technologies Inc
Original Assignee
Kaonetics Technologies Inc
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
Application filed by Kaonetics Technologies Inc filed Critical Kaonetics Technologies Inc
Publication of EP2215498A2 publication Critical patent/EP2215498A2/fr
Publication of EP2215498A4 publication Critical patent/EP2215498A4/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/4802—Travelling-wave MR
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves  involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/4808—Multimodal MR, e.g. MR combined with positron emission tomography [PET], MR combined with ultrasound or MR combined with computed tomography [CT]

Definitions

  • the subject mater presented herein relates generally to imaging devices and methods, and more particularly, to an imaging system that uses a directed-energy device.
  • the energy difference between the nuclear spin states can correspond to a photon at radio frequency (RF) wavelengths.
  • RF radio frequency
  • Resonant absorption of energy by the protons due to an external oscillating magnetic field can occur at what is referred to as the Larmor frequency for the particular nucleus.
  • a practical value of this phenomenon resides in the signal emitted by the excited spins after an excitation signal is terminated.
  • the emitted signal can be a function of at least one and typically several physical properties of the spin that generates the signal and therefore, by examining the emitted signal, the properties of the spin can be determined.
  • the region of interest of a target (human tissue) is subjected to a separate magnetic field which is in the x-y plane and which is near the Larmor frequency, the net aligned moment, or "longitudinal magnetization” may be rotated, or “tipped” to produce a net transverse magnetic moment.
  • a signal can be emitted by the excited spins after the excitation signal is terminated.
  • the emitted magnetic resonance signals can be acquired, digitized and processed to generate a magnetic resonance data set that can be used to produce an image of the target, typically a two dimensional cross section or slice.
  • Known MRI systems can typically includes a plurality of gradient coils positioned about a bore of a magnet to impress a polarizing magnetic field and an RF transceiver system with an RF switch controlled by a pulse module to transmit RF signals to an RF coil assembly, i.e., antenna, and to acquire the magnetic resonance signals emitted by the region of interest within the target.
  • an RF coil assembly i.e., antenna
  • a directed-energy device configured to generate an excitation signal to impinge a region of interest of a target and excite elements therein and receive resonance signals emitted from the region of interest of the target after the excitation signal is terminated can comprise a charged particle generator configured to generate plural energized particles; and a charge transformer configured to receive the plural energized particles that include charged particles from the charged particle generator and to output a wavefront including energized particles that include particles having substantially zero charge; plural gradient coils positioned about a bore of a magnet and configured to impress a polarizing magnetic field on a target; and a communications interface configured to transfer the received resonance signals to a processor configured to produce an image of the region of interest of the target based on the received signals.
  • a method of using a directed- energy device as an imaging system can comprise generating a wavefront that includes particles at substantially zero charge to impinge a target; terminating the wavefront to permit particles within the target to release absorbed energy, return to their previous alignments and emit a signal receiving the emitted signal; processing the received signal; and producing an image of the target area based on the received signal.
  • FIG. 1 shows a functional block diagram of an exemplary embodiment of a directed-energy device used in an imaging system.
  • FIG. 2 shows a simplified cross-sectional view of portions of an exemplary embodiment of directed-energy device used in an imaging system.
  • FIG. 3 shows a flow chart for an exemplary method using an exemplary embodiment of a directed-energy device used in an imaging system.
  • an exemplary embodiment of a directed- energy imaging system can include a charged particle generator 100 configured to generate plural energized particles and a charge transformer 114 configured to receive the plural energized particles that include charged particles from the charged particle generator and to output a wavefront 116 including energized particles that include particles having substantially zero charge.
  • the charged particle generator 100 can be configured to direct the plural energized particles through the charge transformer 114 to propagate through free space until impinging on a target area 118 in, for example, a subject in an MRI device 122.
  • the presence of wavefront 116 at target area 118 can have an excitation effect similar to that produced by the RF system in a known MRI device.
  • elements containing, e.g., protons, in the target area can absorb energy from the wavefront.
  • the protons can release the absorbed energy, return to their previous alignments and, in so doing, emit a signal 120, which can be received by a known communications/detector interface 116 capable of detecting the signal emitted by the excited spins after the excitation signal is terminated, and processed by a processor 128 to produce an image of the target area 118, as explained above.
  • plural gradient coils 124 can be positioned about a bore of a magnet in MRI device 122 to impress a polarizing magnetic field.
  • Gradient coils 124 can be used to spatially encode the positions of protons by varying the magnetic field linearly across the imaging volume.
  • the Larmor frequency can then vary as a function of position in the x, y and z-axes.
  • Gradient coils can be resistive electromagnets powered by amplifiers that can permit adjustments to their field strength and direction.
  • a communications/detector interface 126 can be configured to transfer the received resonance signals emitted from the region of interest of the target after the excitation signal is terminated to a processor 128 configured to produce an image of the region of interest of the target based on the received signals using known image processing methods.
  • the emitted signal 120 from the target area 118 can be alternatively or additionally received by waveguide 110 in the charged particle generator 100, which can essentially operate in reverse when receiving the emitted signal in the form of a reflected and/or attenuated zero charge wavefront.
  • the target area 118 can generate, in response to the substantially zero charge wavefront 116, a signal of a different nature, e.g., an electromagnetic signal, such as an RF signal, microwave signal or visible wavelength signal, to name a few, which can be received and processed using known methods.
  • the plural energized particles 112 can be in the form of a photon particle wave, e.g., a mixture or cross-generation of photons and electrons.
  • energized particle generator 100 can include a DC power supply 102 and DC-to-AC converter 104.
  • charged particle generator 100 can include charged particle emitter 106.
  • charged particle emitter 106 can include any source of radio frequency energy, including microwaves.
  • charged particle emitter 106 may include known magnetrons.
  • charged particle emitter 106 may include solid-state power amplifiers, gyrotrons, traveling wave tubes (TWTs), and/or klystrons.
  • charged particle emitter 106 may be a lower-power source and may generate energy levels of approximately 1 kilowatt (kW) to approximately 100 kW or greater, although the scope is not limited in this respect.
  • an RF signal in charged particle emitter 106, can be formed using known techniques.
  • the RF signal can be combined with an excitation signal, which can form a modulated photon wave.
  • the RF signal can be transmitted to a plurality of directional antenna devices, for example, which may be included in waveguide 110.
  • amplification of the RF signal to a very high signal voltage and subsequent application of this amplified RF signal to the directional antenna devices an ionic discharge at the antennas can occur that can transform the RF signal into a directed particle beam including plural energized particles.
  • waveguide 110 can be configured to minimize backscatter of the energized particles using known techniques.
  • the particle beam can then be further focused and directed via waveguide 110 as an electromagnetic wavefront 112 to impinge on the surface of charge transformer 114.
  • Suitable charged particle emitters that can form a photon particle wave include known energy emission devices such as free electron lasers and discharges or arcs at edges of planar antennae, for example, spark gap generators.
  • charged particle emitter 106 may include a free electron laser, or FEL.
  • a FEL is a laser that shares the same optical properties as conventional lasers such as emitting a beam consisting of coherent electromagnetic radiation which can reach high power, but which uses some very different operating principles to form the beam.
  • gas, liquid, or solid-state lasers such as diode lasers, which rely on bound atomic or molecular states
  • FELs use a relativistic electron beam as the lasing medium, hence the term free electron. This gives them a wide frequency range compared to other laser types, and makes many of them widely tunable, currently ranging in wavelength from microwaves, through terahertz radiation and infrared, to the visible spectrum, to ultraviolet, to soft X-rays.
  • charged particle emitter 106 can include an excitation signal, produced by known signal generation devices, for example.
  • an excitation signal could be a 120 VAC clipped (square) wave that can have an effect of driving a magnetron outside of a typical 2.45 GHz frequency, for example.
  • bandwidths on the order of 0 to 10 GHz can be achieved.
  • charged particle generator 100 can include an energized particle, e.g., photon and/or particle beam or wave, forming module 108.
  • energized particle (photon particle beam or wave) forming module 108 can be positioned in a throat section of a waveguide launcher between charged particle emitter 106 and waveguide 110.
  • energized particle forming module 108 can be made of an electropositive material, such as a polycarbonate sheet. In an embodiment, this material can include DELRIN manufactured by DuPont. In an embodiment, energized particle forming module 108 can act like a roughing filter, i.e., it can start the process of reducing the charge of the charged particles in the mixture of photons and electrons. After passing through energized particle forming module 108, the mixture of photons and electrons can then be directed via waveguide 110 as an electromagnetic wavefront 112 to impinge on the surface of charge transformer 114.
  • an electropositive material such as a polycarbonate sheet. In an embodiment, this material can include DELRIN manufactured by DuPont.
  • energized particle forming module 108 can act like a roughing filter, i.e., it can start the process of reducing the charge of the charged particles in the mixture of photons and electrons. After passing through energized particle forming module 108, the mixture of photons and electrons can then
  • waveguide 110 can include a hollow conducting tube, which may be rectangular or circular, for example, within which EM waves can be propagated. Signals can propagate within the confines of metallic walls, for example, that act as boundaries.
  • waveguide 110 can be configured as a circularly polarized antenna and may radiate substantially circularly polarized energy.
  • waveguide 110 may be linearly polarized and may radiate signals with a linear polarization (e.g., a horizontal and/or a vertical polarization).
  • Antennas in many shapes, such as horns, lenses, planar arrays, and reflectors may be suitable in some of these embodiments.
  • exemplary waveguide 110 can be configured as part of a device that can include a magnetron portion, a throat section of a waveguide launcher area that can include energized particle forming module 108 positioned between charged particle emitter 106 and waveguide 110, and a cone-like portion or horn.
  • a magnetron can be placed in the magnetron portion such that there can be a three-inch gap between the top of the magnetron's cathode and the top of the enclosure.
  • waveguide 110 can be designed to promote sufficient velocity of the photon particle wave that can include a mixture of photons and electrons particles, here designated as EM wavefront 112, moving through the waveguide 110.
  • x refers to a length of exemplary waveguide 110 (which can include energized particle forming module 108) and y refers to a height of an aperture opening at the end of waveguide 110.
  • the ratio of x/y can be approximately 3 to 3.5 to 1 to promote sufficient velocity of the particles moving through the waveguide 110.
  • the aperture opening height (y) is six inches
  • waveguide 110 length can be from 18 to 21 inches.
  • a length of waveguide 110 can be based on the ratio of six times the air gap above an exemplary magnetron's cathode. Using the previously mentioned three-inch gap, this results in a waveguide length of eighteen inches.
  • the aperture opening can be generally rectangular.
  • the aperture opening width can be eight inches for an aperture opening height (y) of six inches.
  • the length of the launcher area before the waveguide 110 can be approximately two inches.
  • the interior surface of exemplary waveguide 110 can be coated with approximately two mils (0.002 inches) of a noble metal, such as 14-carat gold, for example.
  • a noble metal such as 14-carat gold
  • Other noble metals can include ruthenium, rhodium, palladium, osmium, iridium and platinum.
  • Such a coating can improve the gain characteristics of waveguide 110.
  • An example of a suitable coating process that can be used to enhance the performance of antennas or waveguides may be found in U.S. Patent No. 7,221 ,329, the disclosure of which is hereby incorporated by reference in its entirety.
  • EM wavefront 112 can be directed through charge transformer 114.
  • charge transformer 112 can have dielectric and physical characteristics such that the energized charged particles, e.g., electrons, in an EM wavefront 112 can be transformed. While not wishing to be bound by any particular theory, this may be done either by changing characteristics of the particle, or by generation or emission of different particles as a result thereof, thereby creating a wavefront 116 at the output of the charge transformer 114.
  • Wavefront 116 can have the modulation properties of the original RF signal and propagate through free space until impinging on target area 118.
  • a 600 W magnetron can produce a wavefront 116 of about 10 mW/cm2 at the aperture, which can result in about 2 mW/cm2 at 1 meter from the aperture.
  • charge transformer 114 can include an incident surface for receiving the EM wavefront 112 and an exit surface for radiating the wavefront 116.
  • charge transformer 114 can include a composite of glass and/or polycarbonate materials, for example, and can vary in shape.
  • flat plates or panes with parallel surfaces can be used as well as convex lenses of a desired focal length.
  • Hybrid configurations with parallel surfaces at the center and convex surfaces at the edges can also be acceptable configurations.
  • electronegative/electropositive material pair i.e., an electronegative layer next to an electropositive layer, or vice versa, that first receives EM wavefront 112, followed by approximately 1/2 inch of glass or quartz, followed by two electronegative layers.
  • this assembly of layers can be vacuum-sealed in ABS plastic.
  • Suitable materials for the electronegative/electropositive material pair can include known materials that can exhibit electronegative/electropositive behavior.
  • an electropositive material can include a polycarbonate sheet made of DELRIN, for example. Suitable polycarbonate can also be chosen for electronegative layers.
  • plate glass can be sputtered with metal oxides to achieve desired electronegative/electropositive behavior.
  • the approximately 1/2 inch of glass layer can include leaded glass if additional dampening of the emitted zero-charge particle stream is desired.
  • horizontal and/or vertical slits or other openings can be formed into or cut out of charge transformer 114 so that in addition to wavefront 116 propagating from charge transformer 114, charged particles in EM wavefront 112 can also propagate from the device.
  • a controlled amount of charged particles along with wavefront 116 may be useful depending on the operating environment.
  • the slits or other openings may be adjustable by an operator using known methods and/or materials. For example, tape, a slide mechanism, or an aperture mechanism could be used to adjust the slits.
  • Charge transformer 114 may incorporate known coating materials or multiple deposition layers on either the incident surface or the exit surface to aid in the wavefront 116 generation, and/or have abrasion or polishing performed on either surface to enhance desired characteristics of the charge transformer 114. Similarly, side surfaces may have similar operations performed to enhance the desired charge transformer 114 characteristics. Other compositions materials and combinations of materials may be used in the fabrication of the charge transformer 114 to achieve desired transformation effects. Additionally, other geometries may be used for charge transformer 114, including, without limitation, stacking additional charge transformer components in combinations that may reflect, refract or redirect EM wavefront 112.
  • wavefront 116 after exiting charge transformer 114, is shown in FIG. 1 propagating through free space until impinging a target area 118 in, for example, a subject in an MRI device.
  • a target area 118 in, for example, a subject in an MRI device.
  • the presence of wavefront 116 at target area 118 can have an effect similar to that produced by the RF system in a known MRI device.
  • a sighting device such as a laser, rifle scope or gun sight, can be incorporated into an exemplary directed-energy device 101 and used to help direct the wavefront 116.
  • Transforming the plural energized particles within the charge transformer can include laterally aligning the plural energized particles to produce a polarization of the plural energized particles.
  • the plural energized particles can be generated by cross-generation of photons and electrons.
  • charge transformer 114 and waveguide 110 can be made larger or smaller and can have different dimensions and geometries depending, for example, on the power or distance requirements of a particular application.
  • an exemplary charged particle emitter 106 may be configured by those skilled in the art to have multiple voltages, frequencies, and power levels.
  • an antenna can include a first insulating substrate extending in the principal plane of the antenna.
  • the antenna can further include a first radiating element and a connected first conductor and can include a second radiating element and a connected second conductor.
  • the antenna can further include a coupling conductor coupling the second radiating element and the first conductor.
  • the first antenna can further include a first coupler having a first signal conductor and a second signal conductor. The first signal conductor can be coupled to the second conductor, and the second signal conductor can be coupled to the first radiating element.
  • radiating elements when RF signal currents are applied between the first and second signal conductors, radiating elements can resonate and operate as an antenna.
  • the radiation that emanates from a radiating element can tend to emanate from the edge of the element, e.g., the edge of an etched copper, generally flat, shape.
  • a composite radiation field pattern can be shaped and made highly directional.
  • Each antenna configuration may be varied by size and shape to meet frequency requirements and impedance matching requirements according to known "patch radiator" technology. Such directional radiation effects can be incorporated in the embodiments disclosed herein.
  • an exemplary method of using directed-energy imaging system can include generating a wavefront that includes particles at substantially zero charge to impinge a target in step 30; terminating the wavefront to permit particles, e.g., protons, within the target area to release absorbed energy, return to their previous alignments and emit a signal, e.g., a resonance signal, in step 32; receiving the emitted signal in step 34; processing the emitted signal, in step 36; and producing an image of the target area, in step 38.
  • a signal e.g., a resonance signal
  • Generating a wavefront that includes particles at substantially zero charge to impinge a target in step can include combining an RF signal with an excitation signal to produce a modulated signal; generating a modulated photon wave associated with the modulated signal, the modulated photon wave including plural energized particles; directing the modulated photon wave to an incident surface of an charge transformer; transforming the plural energized particles within the charge transformer, wherein the transformed particles are at substantially zero charge; and generating a wavefront at an exit surface of the charge transformer that includes the transformed particles at substantially zero charge.
  • the combining step of generating a wavefront may take the form of superimposing the RF signal upon a signal composed of a square wave riding on a DC voltage level.
  • the modulated photon wave generating step 34 may use, without limiting the scope of the invention, a magnetron as is known in the art or other energy emission device, such as discharges or arcs at edges of planar antennae.
  • transforming the modulated photon wave within the charge transformer can include laterally aligning the photons in the modulated photon wave to produce a polarization of that modulated photon wave. This can be accomplished, for example, by manipulating electron speed of the photons, i.e. slowing the electron speeds to release energy in the form of the broadband wavefront.
  • By controlling the design parameters of the charge transformer e.g., thickness, composition, doping, incident angle of impingement, etc.), desired communication characteristics may be enhanced.
  • the broadband wavefront 116 can behave in a manner that can be described by particle quantum physics rather than by typical communications theory, and can be characterized as being relatively immune to traditional RF interference.
  • the wavefront 116 of the transformed EM radiation 112 can be modified and enhanced based on desired operational characteristics.
  • a zero-charge wavefront as an excitation wave can be focused and can be of high enough energy to provide responses from a target distinct from known magnetic resonance emissions in response to the RF radiation of known MRI systems.
  • the apparatus and methods disclosed herein can provide for imaging three-dimensional targets, for example, of various sizes and compositions using a zero-charge wavefront from a directed energy device.
  • the frequency of the wavefront can be varied to include frequencies within or outside of typical RF frequencies, and can be used in a manner consistent with the excitation energy employed in known imaging techniques, such as the radio frequencies used in magnetic resonance imaging.

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  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • General Health & Medical Sciences (AREA)
  • Radiology & Medical Imaging (AREA)
  • General Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Condensed Matter Physics & Semiconductors (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Biophysics (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Biomedical Technology (AREA)
  • Pathology (AREA)
  • Pulmonology (AREA)
  • Theoretical Computer Science (AREA)
  • Magnetic Resonance Imaging Apparatus (AREA)

Abstract

L'invention concerne un système d'imagerie qui emploie un dispositif à énergie dirigée pouvant être conçu pour générer un signal d'excitation destiné à venir frapper une région intéressante d'une cible et exciter des éléments qui se trouvent dans celle-ci, puis recevoir des signaux de résonance émis depuis la région intéressante de la cible après avoir mis fin au signal d'excitation. Le dispositif à énergie dirigée peut inclure un générateur de particules chargées conçu pour générer une pluralité de particules énergisées et un transformateur de charge conçu pour recevoir la pluralité de particules énergisées qui comprennent des particules chargées provenant du générateur de particules chargées et pour délivrer un front d'onde comprenant des particules énergisées qui incluent des particules ayant une charge sensiblement nulle. Le système d'imagerie peut également inclure une pluralité de bobines à gradient positionnées à proximité d'un noyau d'un aimant et conçues pour appliquer un champ magnétique polarisé à une cible et une interface de communication.
EP08852590A 2007-11-16 2008-11-17 Système d'imagerie à énergie dirigée Withdrawn EP2215498A4 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US98862907P 2007-11-16 2007-11-16
PCT/US2008/012843 WO2009067179A2 (fr) 2007-11-16 2008-11-17 Système d'imagerie à énergie dirigée

Publications (2)

Publication Number Publication Date
EP2215498A2 true EP2215498A2 (fr) 2010-08-11
EP2215498A4 EP2215498A4 (fr) 2011-08-10

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Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5365927A (en) * 1993-11-02 1994-11-22 General Electric Company Magnetic resonance imaging system with pointing device
US5912469A (en) * 1996-07-11 1999-06-15 Nikon Corporation Charged-particle-beam microlithography apparatus
US6124596A (en) * 1997-08-28 2000-09-26 Nikon Corporation Charged-particle-beam projection apparatus and transfer methods
US6567685B2 (en) * 2000-01-21 2003-05-20 Kabushiki Kaisha Toshiba Magnetic resonance imaging apparatus

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
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See also references of WO2009067179A2 *

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WO2009067179A3 (fr) 2009-07-09
WO2009067179A2 (fr) 2009-05-28
EP2215498A4 (fr) 2011-08-10

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