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WO2009081360A1 - Contraste d'image par résonance magnétique amélioré par pompage optique avec moment cinétique orbital - Google Patents

Contraste d'image par résonance magnétique amélioré par pompage optique avec moment cinétique orbital Download PDF

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Publication number
WO2009081360A1
WO2009081360A1 PCT/IB2008/055444 IB2008055444W WO2009081360A1 WO 2009081360 A1 WO2009081360 A1 WO 2009081360A1 IB 2008055444 W IB2008055444 W IB 2008055444W WO 2009081360 A1 WO2009081360 A1 WO 2009081360A1
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WO
WIPO (PCT)
Prior art keywords
light
angular momentum
magnetic resonance
catheter
dipoles
Prior art date
Application number
PCT/IB2008/055444
Other languages
English (en)
Inventor
Daniel R. Elgort
Lucian Remus Albu
Original Assignee
Koninklijke Philips Electronics N.V.
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 Koninklijke Philips Electronics N.V. filed Critical Koninklijke Philips Electronics N.V.
Priority to EP08863841A priority Critical patent/EP2225551A1/fr
Priority to US12/808,385 priority patent/US8765099B2/en
Priority to CN200880121251.8A priority patent/CN101971011B/zh
Publication of WO2009081360A1 publication Critical patent/WO2009081360A1/fr

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Classifications

    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B27/00—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00
    • G02B27/28—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00 for polarising
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N24/00—Investigating or analyzing materials by the use of nuclear magnetic resonance, electron paramagnetic resonance or other spin effects
    • G01N24/08—Investigating or analyzing materials by the use of nuclear magnetic resonance, electron paramagnetic resonance or other spin effects by using nuclear magnetic resonance
    • 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
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/282—Means specially adapted for hyperpolarisation or for hyperpolarised contrast agents, e.g. for the generation of hyperpolarised gases using optical pumping cells, for storing hyperpolarised contrast agents or for the determination of the polarisation of a hyperpolarised contrast agent
    • 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
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/285—Invasive instruments, e.g. catheters or biopsy needles, specially adapted for tracking, guiding or visualization by NMR
    • 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
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/5601—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution involving use of a contrast agent for contrast manipulation, e.g. a paramagnetic, super-paramagnetic, ferromagnetic or hyperpolarised contrast agent
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B27/00—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00
    • G02B27/42—Diffraction optics, i.e. systems including a diffractive element being designed for providing a diffractive effect
    • G02B27/46—Systems using spatial filters

Definitions

  • the present application relates to the diagnostic imaging arts. It finds 5 particular application in magnetic resonance imaging of regions near the surface of a subject's skin or accessible with a probe or catheter, and will be described with particular reference thereto. It is to be appreciated, however, that it is also applicable to other regions or areas, contrast enhanced imaging, spectroscopy and is not limited to the aforementioned applications.
  • MRI magnetic resonance imaging
  • tissue components in the characterization and differentiation of soft tissues.
  • Other applications include fluid chemical analysis of small molecules and biomolecules (e.g. protein-ligand interactions, protein folding, protein structure validation, and protein structure determination), solid state analysis (structural), dynamics of time- variable systems, and the like.
  • Micro MRI systems exist that overcome some of these drawbacks.
  • permanent magnets on the tip of a catheter generate a static magnetic field at the catheter tip.
  • a micro MRI system also has a high quality receiving coil built into the tip, such as a Helmholtz micro coil. This allows for local imaging of blood vessels without the need for external magnets or coils.
  • Gradient coils facilitate Fourier images or point- by-point imaging/analysis to be performed without gradient coils.
  • the present application provides a new and improved optical polarization device which overcomes the above-referenced problems and others.
  • a light-based hyperpolarization device emits light.
  • a phase hologram imparts orbital angular momentum to the light.
  • a spatial filter filters out a portion of the light and allows a portion of the light with a pre-determined amount of orbital angular momentum to pass.
  • At least one optical element directs the light that passes the spatial filter to a region of interest to be hyperpolarized.
  • a magnetic resonance system including a light-based hyperpolarization device that polarizes a selected dipole PH009189
  • An RF system induces resonance in the polarized dipoles and receives resonance signals.
  • a surface probe In accordance with another aspect, a surface probe is provided.
  • a light output unit directs light to penetrate tissue of a patient.
  • a light-based hyperpolarization system imparts orbital angular momentum to generated light. The light to which orbital angular momentum has been imparted is discharged through the light output unit to polarize selected dipoles in the patient.
  • a catheter In accordance with another aspect, a catheter is provided. An elongated portion terminates in a working end configured to be inserted in a patient. A light-based hyperpolarization system imparts orbital angular momentum to generated light. The light to which orbital angular momentum has been imparted is discharged through the light output unit to polarize selected dipoles in the patient.
  • a method of resonance imaging is provided.
  • a selected dipole is polarized via transferred orbital angular momentum.
  • Resonance is induced in the polarized dipoles.
  • Resonance signals are received.
  • One advantage is that blood can be more effectively imaged using nuclear resonance without aid of chemical contrast agents.
  • Another advantage lies in improved access to the subject. Another advantage resides in lower cost.
  • Another advantage lies in improved resonance signal strengths.
  • Another advantage lies in improved resolution.
  • Another advantage of some embodiments is the elimination of large magnetic fields and the associated hardware for generating them, etc. Still further advantages of the present invention will be appreciated by those of ordinary skill in the art upon reading and understand the following detailed description.
  • FIGURE 1 is a diagrammatic illustration of a molecule interacting with an incident photon
  • FIGURE 2 is an optical diagram of a device for generating polarized light beams endowed with orbital angular momentum, in accordance with the present application;
  • FIGURE 3 is an enlarged view of a computer generated phase hologram for endowing incident light with orbital angular momentum, in accordance with the present application;
  • FIGURE 4 is a diffraction projection of a light beam after it passes through the phase hologram of FIGURE 3;
  • FIGURE 5 depicts a spatial filter overlaid on the diffraction projection of FIGURE 4;
  • FIGURE 6 is a diagrammatic illustration of a magnetic resonance imaging apparatus in accordance with the present application.
  • FIGURE 7 is a cutaway view of a catheter that carries orbital angular momentum-endowed light, the catheter being capable of being inserted into a patient, in accordance with the present application.
  • Orbital angular momentum is an intrinsic property of all azimuthal phase-bearing light, independent of the choice of axis about which the OAM is defined.
  • OAM can be transferred from the light to the matter.
  • An analysis of electromagnetic fields shows that there is a flow of electromagnetic energy with one component that travels along the vector of the beam propagation, and a second component that rotates about the axis of the beam propagation.
  • the second component is proportional to the angular change of the potential vector around the beam propagation. This is significant because the rotational energy flow is proportional to /, the OAM value, and the rotational energy transferred to molecules with which the light interacts is increased with the value of the OAM.
  • Light-carrying spin and OAM is absorbed by molecules. Since angular momentum is a conserved quantity, the total angular momentum of the system (both the radiation and the matter) is not changed during absorption and emission of radiation. When a photon is absorbed by an atom, its angular momentum is transferred to the atom. The resulting angular momentum of the atom is then equal to the vector sum of its initial angular momentum plus the angular momentum of the absorbed photon.
  • the Applicant supplements or replaces the function of the Bo field in conventional MRI by electromagnetic radiation endowed with OAM, as described above.
  • FIGURE 2 an exemplary arrangement of optical elements is shown for endowing light with OAM. It is to be understood that any PH009189
  • the described embodiment uses visible light, which interacts with the molecules of interest, and has no damaging effect on living tissue. Light/radiation above or below the visible spectrum, however, is also contemplated.
  • a white light source 22 produces visible white light that is sent to a beam expander 24. In alternate embodiments, the frequency and coherence of the light source can be used to manipulate the signal if chosen carefully, but such precision is not essential.
  • the beam expander includes an entrance collimator 25i for collimating the emitted light into a narrow beam, a concave or dispersing lens 25 2 , a refocusing lens 25 3 , and an exit collimator 25 4 through which the least dispersed frequencies of light are emitted. In one embodiment, the exit collimator 25 4 narrows the beam to a 1 mm beam.
  • the light beam is circularly polarized by a linear polarizer 26 followed by a quarter wave plate 28.
  • the linear polarizer 26 takes unpolarized light and gives it a single linear polarization.
  • the quarter wave plate 28 shifts the phase of the linearly polarized light by 1 A wavelength, circularly polarizing it. Using circularly polarized light is not essential, but it has the added advantage of polarizing electrons.
  • phase hologram 30 An example of a phase hologram 30 is depicted in FIGURE 3.
  • the phase hologram 30 imparts OAM and spin to an incident beam.
  • the value "/" of the OAM is a parameter dependent on the phase hologram 30.
  • the phase hologram 30 is a computer generated element and is physically embodied in a spatial light modulator, such as a liquid crystal on silicon (LCoS) panel, 1280x720 pixels, 20x20 ⁇ m 2 , with a 1 ⁇ m cell gap.
  • the phase hologram 30 could be embodied in other optics, such as combinations of cylindrical lenses or wave plates.
  • the spatial light modulator has the added advantage of being changeable, even during a scan, with a simple command to the LCoS panel.
  • the bright spot (Airy disk) 32 in the middle represents the 0 th order diffraction, in this case, that is light with no OAM.
  • the circles 34 adjacent the bright spot 32 represent diffracted beams of different harmonics that carry OAM. This distribution results because the probability of OAM interaction with molecules falls to zero at points far from the center of the light beam or in the center of the light beam. The greatest chance for interaction occurs on a radius corresponding to the maximum field distribution, that is, for circles close to the Airy disk. Therefore, the maximum probability of OAM interaction is obtained with a light beam with a radius as close as possible to the Airy disk radius.
  • a spatial filter 36 is placed after the holographic plate to selectively pass only light with OAM and spin.
  • An example of such a filter is shown in FIGURE 5.
  • the 0 th order spot 32 always appears in a predictable spot, and thus can be blocked.
  • the filter 36 allows light with OAM to pass. Note that the filter 36 also blocks the circles that occur below and to the right of the bright spot 32. Since OAM of the system is conserved, this light has OAM that is equal and opposite to the OAM of the light that the filter 36 allows to pass. It would be counterproductive to let all of the light pass, because the net OAM transferred to the target molecule would be zero. Thus, the filter 36 only allows light having OAM of one polarity to pass.
  • the diffracted beams carrying OAM are collected using concave mirrors 38 and focused to the region of interest with a fast microscope objective lens 40.
  • the mirrors 38 may not be necessary if coherent light were being used.
  • a faster lens (having a high f-number) is desirable to satisfy the condition of a beam waist as close as possible to the size of the Airy disk.
  • the lens 40 may be replaced or supplemented with an alternative light guide or fiber optics.
  • the polarized light is used to supplement the B 0 field of an existing scanner.
  • the light is emitted parallel to the B 0 field, so that the effects complement each other, that is, the nuclei are aligned in the same direction due to both the B 0 field and the polarized light.
  • Traditional spatial encoding and RF excitation can be used, but with the optical alignment, the resonance signal can be seven to eight orders of magnitude stronger, leading to increased signal to noise ratio, better signal strength, and improved resolution, on the order of micrometers.
  • the PH009189 the PH009189
  • polarized light beam is applied along a direction other than parallel to the B 0 field, to produce concurrent dipoles with different relaxation orientations.
  • the typical B 0 field is replaced entirely by optical perturbation.
  • the large, complex main magnet is eliminated, greatly freeing up space and making the subject more accessible.
  • resonance signals would only be received from dipoles accessible by the optical delivery system.
  • Spatial encoding is achieved, for example, by gradient magnetic fields produced by weaker, homogeneous magnets.
  • spatial encoding is achieved optically. Polarized light along one axis serves to align the dipoles along a single direction, while an array of light generators along another axis perform the spatial encoding. The light is used to spatially encode the resonance by phase encoding and frequency encoding. Frequency encoding is provided by magnets or by light.
  • the light emitting system previously described may be embodied in a needle or catheter 68 in FIGURE 6 and inserted directly into the bloodstream.
  • the light source 22 is conveniently located outside of the intravenous device and fiber optics is used to channel the light thereto.
  • the catheter 68 is then inserted into the subject, such as through the femoral artery, and advanced to the region or anatomy of interest.
  • the light aligns dipoles in illuminated vessel walls or other adjacent tissues analogous to a conventional B 0 field.
  • the aligned dipoles are caused to resonate by the application of RF signals by an RF coil in the tip of the catheter 68 or by external RF coils.
  • the induced resonance signals are received by the RF coils in the tip of the catheter for a high signal-to-noise ratio.
  • External RF receive coils e.g. surface coils are also contemplated.
  • the resonance can be spatially encoded in various ways.
  • the resonance is excited in and detected from a single voxel at a time.
  • external or at-the-tip gradient magnetic field coils phase- and frequency-encode the resonance.
  • a permanent magnet or magnetic field coil adjacent the tip encodes frequency and the OAM enhanced light is used for phase encoding.
  • a very low field magnet provides a weak Bo field aligned with the OAM-endowed induced polarization.
  • the B 0 field determines the resonance frequency. The higher the Bo field, the higher the resonance frequency. High PH009189
  • B 0 fields generally have high associated magnet costs and larger magnets that inhibit patient access.
  • blood passing by the light emitter at the tip of the catheter 68 or a surface probe 66 is aligned, particularly hyperpolarized, and it can be imaged as it flows to a downstream portion of the body.
  • the light source illuminates blood flowing through the carotid artery
  • the hyperpolarized blood exhibits high signal strengths in the blood vessels in the brain.
  • the carotid artery passes close to the surface, it can be illuminated from the surface without using an invasive procedure such as a catheter.
  • the polarized light can be used in lieu of, or to supplement traditional chemical contrast in a conventional MRI system.
  • polarized light is not as time-sensitive as some chemical contrast agents, as the transit time to the patient and ultimately to the region of interest would not be critical. Also, chemical contrast agents carry the disadvantage of being hard on the patient's kidneys and liver, and elimination of the use of such chemical contrast agents would therefore be beneficial.
  • OAM organic metal-oxide-semiconductor
  • Infrared light can be used to increase light penetration, for example, to illuminate sub-dermal structures, but at the cost of interaction strength.
  • OAM can be imparted to any electromagnetic wave, not just visible light. Using shorter wavelengths would bring the advantage of having greater sub-dermal penetration, but also carrying with it the disadvantage that penetrating radiation is potentially damaging to tissue.
  • the OAM-endowed light- emitting device as described above can be used in conjunction with a magnetic resonance scanner 40.
  • the magnetic resonance scanner 40 can be an open field system (open MRI system) that includes a vertical main magnet assembly 42.
  • the main magnet assembly 42 produces a substantially constant main magnetic field oriented along a vertical axis of an imaging region.
  • a vertical main magnet assembly 42 is illustrated, it is to be PH009189
  • a gradient coil assembly 44 produces magnetic field gradients in the imaging region for spatially encoding the main magnetic field.
  • the magnetic field gradient coil assembly 44 includes coil segments configured to produce magnetic field gradient pulses in three orthogonal directions, typically longitudinal or z, transverse or x, and vertical or y directions. Both the main magnet assembly 42 and the gradient field assembly 44 in some embodiments are used along with optical polarization.
  • a radio frequency coil assembly 46 (illustrated as a head coil, although surface and whole body coils are also contemplated) generates radio frequency pulses for exciting resonance in dipoles of the subject.
  • the radio frequency coil assembly 46 also serves to detect resonance signals emanating from the imaging region.
  • the radio frequency coil assembly 46 can be used to supplement optical perturbation of previously established polarization.
  • Gradient pulse amplifiers 48 deliver controlled electrical currents to the magnetic field gradient assembly 44 to produce selected magnetic field gradients.
  • a radio frequency transmitter 50 preferably digital, applies radio frequency pulses or pulse packets to the radio frequency coil assembly 46 to excite selected resonance.
  • a radio frequency receiver 52 is coupled to the coil assembly 46 or separate receive coils to receive and demodulate the induced resonance signals.
  • a sequence controller 54 communicates with the gradient amplifiers 48 and the radio frequency transmitter 50 to supplement the optical manipulation of the region of interest.
  • the sequence controller 54 may, for example, produce selected repeated echo steady-state, or other resonance sequences, spatially encode such resonances, selectively manipulate or spoil resonances, or otherwise generate selected magnetic resonance signals characteristic of the subject.
  • the generated resonance signals are detected by the RF coil assembly 46, communicated to the radio frequency receiver 52, demodulated and stored in a k-space memory 56.
  • the imaging data is reconstructed by a reconstruction processor 58 to produce one or more image representations that are stored in an image memory 60.
  • the reconstruction processor 58 performs an inverse Fourier transform reconstruction. PH009189
  • the resultant image representation(s) is processed by a video processor 62 and displayed on a user interface 64 equipped with a human readable display.
  • the interface 64 is preferably a personal computer or workstation. Rather than producing a video image, the image representation can be processed by a printer driver and printed, transmitted over a computer network or the Internet, or the like.
  • the user interface 64 also allows a radiologist or other operator to communicate with the sequence controller 54 to select magnetic resonance imaging sequences, modify imaging sequences, execute imaging sequences, and so forth.
  • a surface probe device 66 that carries the optical device depicted in FIGURE 2 is pressed against the carotid artery(s) where it is sufficiently close that the optical light will penetrate to the blood inside.
  • the optical device can be used to align or hyperpolarize the nuclei of molecules in the blood flowing past the device. These molecules can then be imaged with the device 40 as they flow through the subject's bloodstream.
  • a series of volume images of the brain are generated as the hyperpolarized blood flows into the brain and/or as it washes out.
  • a single volume image is generated or selected, which illustrates the blood flow in the brain. The images can illustrate penetration of blood into brain tissue, arterial flow, venous flow, etc.
  • an inserted catheter or needle probe, as described above, is used to hyperpolarize blood upstream from a region of interest.
  • the catheter 68 and the main magnets 42 can work together to align the dipoles of interest, the gradient coil assembly 44 can provide spatial encoding, and the RF coils system 46 can excite and receive resonance.
  • the hyperpolarizing device is contained entirely within the catheter 68 system.
  • the catheter 68 includes an elongated portion 70 and a working end 72 configured for insertion into a patient.
  • the elongated portion 70 includes fiber optics or other light guides to transmit light from the light source 22 to the working end 72.
  • the catheter 68 includes the magnetic elements necessary for magnetic resonance imaging at the working end; the working end includes a magnet 74 for producing a substantially uniform magnetic field at the working end 72 of PH009189
  • a gradient magnetic coil 76 for encoding the main magnetic field with gradient fields
  • an RF coil 78 for exciting and receiving magnetic resonance.
  • polarized light coming through the elongated portion 70 encounters a partially mirrored plate 80 that allows a portion of light to pass to a first objective lens 82. Another portion of light is reflected to a first mirror 84 and on to a second mirror 86 where it then passes through a second objective lens 88, which is oriented orthogonally to the first objective lens. Other optical orientations are certainly possible to arrive at the same result and are also contemplated.
  • a mechanical shutter 90 may be provided so that the orthogonally oriented light may be selectively blocked when it is not desired.
  • light from the second objective lens 86 can be used to selectively optically manipulate dipoles polarized by light from the first objective lens 82.

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  • General Physics & Mathematics (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Condensed Matter Physics & Semiconductors (AREA)
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  • General Health & Medical Sciences (AREA)
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  • Optics & Photonics (AREA)
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Abstract

En imagerie par résonance magnétique (IRM), des dipôles magnétiques sélectionnés chez un sujet sont alignés avec un champ magnétique principal pour réaliser par la suite une manipulation, et les signaux reçus après cette manipulation sont utilisés pour créer des représentations du sujet sous forme d'images. Un inconvénient est que même des champs magnétiques puissants peuvent seulement aligner un très faible pourcentage de dipôles dans la région du champ. Un rayonnement magnétique doté d'un moment cinétique orbital (OAM) aligne un pourcentage bien plus élevé de dipôles le long du passage du rayonnement ; jusqu'à 100 % des dipôles peuvent être alignés dans une région. Par conséquent, la puissance des signaux de résonance émis à partir de la région est supérieure de plusieurs ordres de grandeur à celle des signaux émis quand des techniques IRM traditionnelles sont utilisées. Tous les rayonnements électromagnétiques, y compris la lumière visible, peuvent être dotés d'un OAM et utilisés pour hyperpolariser une région d'intérêt.
PCT/IB2008/055444 1996-04-08 2008-12-19 Contraste d'image par résonance magnétique amélioré par pompage optique avec moment cinétique orbital WO2009081360A1 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
EP08863841A EP2225551A1 (fr) 2007-12-20 2008-12-19 Contraste d'image par résonance magnétique amélioré par pompage optique avec moment cinétique orbital
US12/808,385 US8765099B2 (en) 1996-04-08 2008-12-19 Magnetic resonance imaging hyperpolarization of liquids or solids by light with orbital angular momentum
CN200880121251.8A CN101971011B (zh) 2007-12-20 2008-12-19 利用通过具有轨道角动量的光超极化液体或固体的磁共振成像

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Application Number Priority Date Filing Date Title
US1521007P 2007-12-20 2007-12-20
US60/015,210 2007-12-20

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