WO2000072031A1 - Procede d'imagerie par rmn utilisant des solutions d'agents de contraste provenant de la dissolution de materiaux hyperpolarises - Google Patents

Procede d'imagerie par rmn utilisant des solutions d'agents de contraste provenant de la dissolution de materiaux hyperpolarises Download PDF

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WO2000072031A1
WO2000072031A1 PCT/GB2000/001888 GB0001888W WO0072031A1 WO 2000072031 A1 WO2000072031 A1 WO 2000072031A1 GB 0001888 W GB0001888 W GB 0001888W WO 0072031 A1 WO0072031 A1 WO 0072031A1
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agent
imaging
imaging agent
polarised
nuclear spin
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PCT/GB2000/001888
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English (en)
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Oskar Axelsson
Haukur Johannesson
Jan Henrik Ardenkjaer-Larsen
Ib Laursen
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Nycomed Imaging As
Moy, David
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Priority to AU45986/00A priority Critical patent/AU4598600A/en
Priority to GB0126355A priority patent/GB2364785B/en
Publication of WO2000072031A1 publication Critical patent/WO2000072031A1/fr
Priority to US09/990,512 priority patent/US20020058869A1/en

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    • 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

Definitions

  • the present invention relates to methods of magnetic resonance imaging (MRI) , and in particular to the use therein of contrast agent solutions formed from the dissolution of hyperpolarised materials.
  • MRI magnetic resonance imaging
  • contrast agent solutions formed from the dissolution of hyperpolarised materials.
  • a novel polarisation method of solid materials is disclosed.
  • Magnetic resonance imaging is a diagnostic technique that has become particularly attractive to physicians as it is non- invasive and does not involve exposing the patient under study to potentially harmful radiation such as X-rays.
  • MR contrast agents e.g. paramagnetic metal species
  • the imaging nuclei the nuclei whose MR signal is used to generate the image
  • image contrast is enhanced.
  • MR signal strength is also dependent on the population difference between the nuclear spin states of the imaging nuclei. This is governed by a Boltzmann distribution and is dependent on temperature and magnetic field strength. However, in MR imaging contrast enhancement has also been achieved by utilising the "Overhauser effect" in which an esr transition in an administered paramagnetic species is coupled to the nuclear spin system of the imaging nuclei.
  • SUBSTITUTE SHEET fRULE 2B example conventional OMRI contrast agents or hyperpolarised gases to achieve ex vivo nuclear spin polarisation of non zero nuclear spin nuclei in an administrable MR imaging agent.
  • polarising agent is meant any agent suitable for performing ex vi vo polarisation of an MR imaging agent.
  • the ex vivo method has the advantage that it is possible to avoid administering the whole of, or substantially the whole of, the polarising agent to the sample under investigation, whilst still achieving the desired nuclear spin polarisation in the MR imaging agent.
  • the method is less constrained by physiological factors such as the constraints imposed by the administrability, biodegradability and toxicity of OMRI contrast agents in in vivo techniques.
  • MRI methods involving ex vivo nuclear spin polarisation may be improved by using nuclear spin polarised MR imaging agents comprising in their molecular structure nuclei capable of emitting MR signals in a uniform magnetic field (e.g. MR imaging nuclei such as 13 C or 15 N nuclei) and capable of exhibiting a long T 2 relaxation time, and preferably additionally a long T 2 relaxation time.
  • nuclear spin polarised MR imaging agents comprising in their molecular structure nuclei capable of emitting MR signals in a uniform magnetic field (e.g. MR imaging nuclei such as 13 C or 15 N nuclei) and capable of exhibiting a long T 2 relaxation time, and preferably additionally a long T 2 relaxation time.
  • Such agents are referred to hereinafter as "high ⁇ agents”.
  • a high T ⁇ agent a term which does not include ⁇ ⁇ .
  • 2 0 r will generally be water-soluble and have a T 2 value of at least 6 seconds in D 2 0 at 37°C and at a field of 7T, preferably 8 sees or more, more preferably 10 sees or more, especially preferably 15 sees or more, more especially preferably 30 sees or more, yet more especially preferably 70 sees or more, even yet more especially preferably 100 sees or more.
  • the molecules of a high r T 1 agent will preferably contain the MR imaging nucleus in an amount greater than its natural isotopic abundance (i.e. the agent will be "enriched" with said nuclei) .
  • hyperpolarised MR contrast agents in MR investigations such as MR imaging has the advantage over conventional MR techniques in that the nuclear polarisation to which the MR signal strength is proportional is essentially independent of the magnetic field strength in the MR apparatus.
  • the highest obtainable field strengths in MR imaging apparatus are about 8T, while clinical MR imaging apparatus are available with field strengths of about 0.2 to 1.5T. Since superconducting magnets and complex magnet construction are required for large cavity high field strength magnets, these are expensive.
  • Using a hyperpolarised contrast agent since the field strength is less critical it is possible to make images at all field strengths from earth field (40-50 ⁇ T) up to the highest achievable fields.
  • MR imaging agents e.g. high T j agents
  • MR imaging agents may be nuclear spin polarised in the solid state prior to being dissolved in a physiologically tolerable solvent and subsequently administered as a hyper-polarised solution to the sample under investigation.
  • the polarisation is effected by means of a polarising agent
  • the whole, substantially the whole, or at least a portion of the polarising agent can be separated from the MR imaging agent prior to administration.
  • this can be achieved by spin refrigeration or by irradiating with circularly polarised light, as described below.
  • the spin refrigerator technique or spin refrigeration involves placing the material which is to be spin polarised, doped with or in intimate admixture with the paramagnetic ions, in a strong magnetic field at a low temperature and repeatedly or continuously reorienting the material relative to the magnetic field, e.g. about an axis perpendicular to the field axis. See for example Jeffries in Proc . Int. Conf . on Polarised Targets and Ion Sources, Saclay, France, 1967, 147 (1966) and McColl et al . Phys Rev B. 7: 2917 (1970) and references therein.
  • the present invention relates in one aspect to the use of light irradiation to generate nuclear-spin hyperpolarized MR imaging agents by irradiation of a solid compound having a singlet electronic ground state or alternatively generating hyperpolarized MR imaging agents by spin refrigeration.
  • the former is achieved by generation of a polarized triplet electronic state in the solid compound and transformation of the electronic state polarization into a nuclear spin state population difference in a solid soluble MR imaging agent which contains non zero nuclear spin (1*0) nuclei which is higher than the equilibrium population difference, i.e. into a nuclear spin state polarization of the MR imaging agent .
  • the present invention provides a method of magnetic resonance investigation of a sample, preferably a human or non-human animal body (e.g. a mammalian, reptilian or avian body), said method comprising:
  • nuclear spin polarising a solid MR imaging agent i.e. a material containing in its molecular structure a non-zero nuclear spin nucleus, preferably a high Tj agent, especially preferably a water-soluble high T 2 agent ) by '
  • (v) optionally generating an image, dynamic flow data, diffusion data, perfusion data, physiological data (e.g. pH, p0 2 , pC0 2 , temperature or ionic concentrations) or metabolic data from said detected signals.
  • physiological data e.g. pH, p0 2 , pC0 2 , temperature or ionic concentrations
  • the invention may involve the sequential steps of nuclear spin polarising (otherwise referred to herein as "hyperpolarising” ) a solid MR imaging agent by polarisation transfer from paramagnetic electron spins with large anisotropy factors producing a hyperpolarised solution from said high T x agent, administering the hyperpolarised MR imaging agent (preferably in solution but optionally as a finely divided particulate, and preferably in the absence of a portion of, more preferably substantially the whole of, the paramagnetic species involved in transferring the polarisation) , and conventional in vivo MR signal generation and measurement .
  • the MR signals obtained in this way may be conveniently converted by conventional manipulations into 2-, 3- or 4-dimensional data including flow, diffusion, physiological or metabolic data.
  • steps (i) and (ii) of the method of the invention comprises the following: i) irradiating a solid compound having a singlet electronic ground state and containing a non zero nuclear spin nucleus with light to generate an excited polarized triplet electronic state of said agent; ii) transforming electronic polarization of said solid compound into a nuclear spin polarization in a soluble solid MR imaging agent to form a nuclear spin polarised MR imaging agent; iii) dissolving said polarised MR imaging agent in an aqueous medium, preferably a physiologically tolerable medium, e.g.
  • the invention provides a process for the preparation of a nuclear spin polarised MR imaging agent, said process comprising irradiating a solid compound having a singlet electronic ground state and containing a non zero nuclear spin nucleus with light to generate an excited polarized triplet electronic state of said agent ; transforming electronic polarization of said solid compound into a nuclear spin polarization in a soluble solid MR imaging agent to form a nuclear spin polarised MR imaging agent, optionally dissolving said MR imaging agent in an aqueous medium (preferably a physiologically tolerable medium) , and optionally storing said polarised MR imaging agent at a reduced temperature, e.g.
  • liquid nitrogen temperature or below for example at 10K (the working temperature of a commercial closed-cycle cryo-cooler (APD-cryogenics) ) or liquid helium at 4.2K, and at a magnetic field of greater than 10 mT, preferably greater than 0.1T, more preferably greater than 0.5T, even more preferably greater than 2T.
  • 10K the working temperature of a commercial closed-cycle cryo-cooler (APD-cryogenics)
  • liquid helium at 4.2K
  • a magnetic field of greater than 10 mT preferably greater than 0.1T, more preferably greater than 0.5T, even more preferably greater than 2T.
  • the process of nuclear spin polarisation in the method of the invention involving irradiating with circularly polarised light essentially involves two stages. First, a polarised electronic triplet state must be formed and second this electronic polarisation is harnessed to generate a nuclear spin polarisation.
  • polarised electronic triplet state is meant the case where the three sub-levels of the triplet state are not equally populated.
  • the lowest electronic triplet state, T x is formed by intersystem crossing from the first excited singlet state, S 1 , which can be reached from the singlet ground state, S 0 , by light absorption and internal conversion (radiationless decay) .
  • This triplet state, T has three different sub-levels, T 2 , T x and T lz , which are populated to different extents by the intersystem crossing.
  • This has the advantage that a low temperature is not required for the generation of the polarised electronic triplet state. It has, however, the disadvantage of relatively poor efficacy where the irradiated solid MR imaging agent is a powder where many different crystals with different orientations are mixed.
  • the lifetime of the triplet state is short compared to the lifetime of the individual triplet sublevels (i.e. the rate of decay of the triplet state should be faster than the rate of interconversion between different triplet sub-levels) .
  • the rate of decay of the triplet state should be faster than the rate of interconversion between different triplet sub-levels.
  • a third way of generating polarised electronic triplets has not been used before for solid materials. If the triplet state is irradiated with positively, circularly polarised light of such a wavelength that it is in resonance with the Tj-T 2 transition, where T 2 is the next highest electronic triplet state above T l r only transitions where the magnetic and the electronic quantum number are both increased are allowed. This means that for a hypothetical case, T ly -T 2i , T ly -T 2z transitions are allowed but no transitions from T lz will be allowed. The T 2z state then relaxes quickly to give a mixture of the three sublevels of T : .
  • the present invention provides a process for the preparation of a polarised electronic triplet state of a solid compound having a singlet electronic ground state, preferably a water-soluble compound containing at least one non- zero nuclear spin nucleus, said process comprising irradiating said compound in a solid state with a first radiation (i.e. light) of a wavelength selected to excite said compound from a ground singlet electronic state to an excited singlet electronic state and with a positively or negatively, circularly polarised second radiation of a wavelength selected to excite said compound from the lowest triplet electronic state to the next-to-lowest triplet electronic state.
  • a first radiation i.e. light
  • the second part of the nuclear spin polarisation process involves an efficient transfer of polarisation from the electrons to non zero nuclear spin nuclei in the solid material.
  • the I ⁇ O nuclei in question may be in the electronically polarised compound or may be in a separate compound mixed therewith.
  • the MR imaging agent is the same as the compound which is excited into a polarised triplet electronic state.
  • MIONP Microwave Induced Optical Nuclear Polarisation
  • the solid effect in its pure form occurs in a material that has been doped with a paramagnetic species that has an ESR linewidth, ⁇ v e , that is smaller than the resonance frequency of the nuclear spin v n at a given magnetic field, as shown in Figure 2 of the accompanying drawings.
  • the solid effect works at two frequencies, v e - v n and ⁇ + v n .
  • the transitions involves the simultaneous inversion of an electron and a nuclear spin, a process which is forbidden to a first approximation and slow in real time.
  • the solid effect gradually changes to what is called the differential solid effect as the linewidth of the unpaired electron becomes equal to or greater than the resonance frequency of the nuclear spin. This means that at low fields the differential solid effect will be the normal case .
  • the ESR line of a solid material will generally be inhomogenously broadened, that is, it can be looked upon as a collection of spin packets with slightly different resonance frequencies .
  • the differential solid effect will lead to poor efficiency at low magnetic fields or with broad ESR lines.
  • This can be remedied by use of the integrated solid effect, in which the irradiation frequency is swept from one side of the line to the other. Assuming the direction of the sweep is from low to high frequency, the effect for one spin packet will then be that initially the forbidden transition leading to positive polarisation will be encountered and utilised, leading to a build-up of the nuclear polarisation. As the frequency increases, the main ESR absorption of the electron will be irradiated and the population is inverted. Now, when the high frequency forbidden transition is irradiated it will also lead to positive polarisation of the nuclear spins since the electron population has been inverted.
  • thermal mixing When the concentration of unpaired spins is high enough, a process called thermal mixing may be utilised. As opposed to the solid effect described above, this is an allowed process.
  • the requirement is that the linewidth of the ESR absorption is larger than the nuclear Larmor frequency.
  • the non zero nuclear spin nucleus in the MR imaging agent may be present in its naturally occurring isotopic abundance. However where the nucleus is a non- preponderant isotope (e.g. 13 C where 12 C is the preponderant isotope) it will generally be preferred that the nucleus is present at a higher than normal level .
  • a non- preponderant isotope e.g. 13 C where 12 C is the preponderant isotope
  • a chromophore in the agent is desirable if light absorption is desired and suitable examples include carbonyl groups, auxochromes, e.g. chlorine or bromine atoms, which enhance extinction coefficients of chromophores they are attached to, are also preferably present. These substituents both enhance the extinction coefficient and the efficiency of the intersystem crossing. Heterocyclic chromophores are also quite attractive since they often have high intersystem crossing efficiency, good water solubility, and are easy to label with 1J C.
  • the MR imaging agent be doped with or be intimately mixed with (e.g. milled together with) a paramagnetic material, e.g. paramagnetic metal ions.
  • the paramagnetic material preferably has a Lande g-tensor where one of the principal components is less than or equal to 0.004 and where the other principal component is at least 0.01, preferably at least 0.1, more preferably at least 1, or even more prferably at least 10.
  • paramagnetic species include transition metal ions, for example Ni 2+ ions, lanthanide and actinide ions, especially lanthanide ions, in particular Ce 3+ and Yb 3+ , most especially Ce 3+ and Yb 3+ ions in crystals with a symmetry axis of order three or more.
  • paramagnetic ions will reduce the relaxation times of the imaging nuclei in the MR imaging agent and thus they are preferably separated as thoroughly as possible from the MR imaging agent once spin refrigeration has taken place.
  • at least 80% of the paramagnetic material is removed, particularly preferably 90% or more, especially preferably 95% or more, most especially 99% or more.
  • preferred polarisation transfer agents are those which can be conveniently and rapidly separated from the polarised MR imaging agent using known techniques as discussed below. However where the polarisation transfer agent is non- toxic, the separation step may be omitted.
  • the separation step of the method of the invention it is desirable to remove substantially the whole of the polarisation transfer agent from the composition (or at least to reduce it to physiologically tolerable levels) as rapidly as possible.
  • Many physical and chemical separation or extraction techniques are known in the art and may be employed to effect rapid and efficient separation of the polarisation transfer agent and high Ti agent.
  • the more preferred separation techniques are those which can be effected rapidly and particularly those which allow separation in less than one second. Separation can be achieved for example by dissolving the spin polarised MR imaging agent in a solvent (or solvent mixture) and passing the resultant solution through a cation exchange medium or another cation immobilising system (e.g.
  • a cation exchange resin or an immobilised chelating agent or by filtering the solution where a paramagnetic material which is not soluble in the solvent system has been used or by precipitation of the paramagnetic metal from solution followed by filtration.
  • Dissolution in a physiologically tolerable solvent, followed by passage through a cation exchange resin is preferred as it is rapid and yields a solution which can be used without further treatment .
  • physiologically tolerable solvent we mean any solvent, solvent mixture or solution that is tolerated by the human or non-human animal body, e.g. water, aqueous solutions such as saline or aqueous alkanolic solutions, perfluorocarbons, etc.
  • the doped crystal is cooled, e.g. to lower than 80K, more preferably lower than 20K, even more preferably lower than 4.2K, most preferably lower than or equal to IK. This may be done by immersion in a liquid helium bath, preferably pumped to IK.
  • the crystal is mounted in such a way that it can be rotated, thus enabling the axis of symmetry of the crystal field to make any angle with the main magnetic field.
  • the magnetic field is preferably greater than 10 mT, more preferably greater than 0.1T, even more preferably greater than 0.5T, yet more preferably greater than or equal to IT, e.g. 1-7T. Should the axis of symmetry of the crystal be threefold, or even higher, then the system is uniaxial with respect to the second-rank g- tensor, i.e. there are only two distinct principal components ,
  • one of the two principal components should be at least as small as the g- factor of the nucleus, whilst the other, either g ⁇ or g , should be much larger.
  • the orientation dependence of the g-factor can be written as:
  • ⁇ angle between the crystal symmetry axis and the magnetic field.
  • the spin lattice relaxation time of the ion is anisotropic, i.e. the relaxation time should preferably depend on the orientation of the crystal with respect to the magnetic field.
  • the relaxation time should preferably depend on the orientation of the crystal with respect to the magnetic field.
  • an orientation producing a large g-factor should coincide with a short relaxation time, whilst one corresponding to a g-factor equal to the nuclear g-factor should have a long relaxation time.
  • the crystal is oriented such that the relaxation time is short and the g-factor is large, the ions and the nuclei are thermally separated and therefore the ions will quickly become polarised.
  • rotating the crystal to an orientation corresponding to a long relaxation time and a small g-factor will reduce the spin temperature of the paramagnetic ion and the two spin systems will now be in thermal contact and at the same time isolated from the lattice.
  • Thermal mixing will reduce the spin temperature of the nuclei and increase the temperature of the ions.
  • Rotation back to the original orientation will cool the ions to their initial temperature, i.e. the lattice temperature.
  • the whole procedure is cyclically repeated to achieve maximum polarisation.
  • the technique of spin refrigeration is not limited to the polarisation of single crystals, although this is the preferred case. Nevertheless, the technique can be used for powder samples. In the latter case, the efficiency of the technique is reduced compared to the polarisation of single crystals, with each crystallite in the powder developing its own polarisation. With powder samples, the average polarisation will be 87% (10 ⁇ /36) of the polarisation of an optimally oriented single crystal .
  • the crystal can be rotated physically.
  • the magnetic field can be rotated electronically, the advantage being that this enables both discrete and rapid rotation which is more efficient than continuous rotation of the crystal.
  • the large magnetic anisotropi within an ion in a crystal is utilised.
  • the required energy correspondence between the electronic and nuclear transitions is also found for many ions when the c-axis is parallel to the magnetic field when crossing of the lowest electronic Zeeman levels may occur.
  • An example of such an ion is Ni 2+ in sapphire.
  • the lowest level is a singlet and in zero field a Kramers doublet is found at 30 GHz above the singlet (see Figure 4 of the accompanying drawings) . As the field increases, the lowest of the doublet levels will approach the singlet and at a field of about IT the two levels will cross each other, and hence the electronic and nuclear Zeeman transition energies will be the same.
  • the spin refrigeration technique described has several major advantages over conventional dynamic nuclear polarisation (DNP) techniques.
  • DNP dynamic nuclear polarisation
  • One embodiment of the invention provides a method as described above wherein the hyperpolarised solid sample of the MR imaging agent retains its polarisation when transported in a substantially uniform magnetic field and at low temperature; in this way the agent can be hyperpolarised at a site remote from its end use and transported to its place of use in a magnetic field and at a low temperature and there dissolved and administered.
  • the magnetic field is preferably greater than 10 mT, more preferably greater than 0.1T, even more preferably greater than 0.5T, yet more preferably greater than IT.
  • it can be transported in a low temperature transporter as described in WO99/17304.
  • low temperature in this context is preferably meant lower than 80K, more preferably lower than 4.2K, most preferably about IK.
  • a further embodiment of the invention provides a method as described above wherein the hyperpolarised solution thus formed retains its polarisation when transported in a magnetic field, and preferably at a low temperature, i.e. in frozen form.
  • the magnetic field is preferably greater than 10 mT, more preferably greater than O.IT, even more preferably greater than 0.5T, yet more preferably greater than IT.
  • a yet further embodiment of the invention provides a method as described above wherein a magnetic field is present during the dissolution stage.
  • the magnetic field is preferably greater than 10 mT, more preferably greater than 0.1T, even more preferably greater than 0.5T, yet more preferably greater than IT.
  • Examples of compounds which may be used as MR imaging agents according to the method of the invention involving irradiating with circularly polarised light include
  • ring carbons are optionally replaced by lj C
  • carboxy groups are optionally replaced by hydroxyalkyloxycarbonyl or hydroxyalkylaminocarbonyl groups
  • non- labile hydrogens are optionally replaced by 'H
  • ring carbons in heterocyclic rings are optionally substituted by solubilising groups, e.g. hydroxyalkyl , hydroxyalkylaminocarbonyl , hydroxyalkylcarbonylamino groups, and where alkyl groups unless otherwise stated conveniently contain up to six carbons.
  • the MR imaging agent should of course be physiologically tolerable or be capable of being presented in a physiologically tolerable form.
  • the MR imaging agent should preferably be strongly nuclear spin polarisable (for example, to a level of greater than 5%, preferably greater than 10%, more preferably greater than 25%) and have an MR imaging nucleus with a long T : relaxation time under physiological conditions, e.g. 1J C, 15 N or 29 Si .
  • a long T x relaxation time is meant that T 1 is such that once nuclear spin polarised, the MR imaging agent will remain so for a period sufficiently long to allow the imaging procedure to be carried out in a comfortable time span.
  • Significant polarisation should therefore be retained for at least Is, preferably for at least 60s, more preferably for at least 100s and especially preferably 500s or longer.
  • Quadrupolar nuclei (e.g. 14 N) should preferably not be included in the MR imaging agent although they may be present in counterions or other dissolved components of a contrast medium containing the MR imaging agent .
  • the MR imaging agent should preferably be relatively small (e.g. molecular weight less than 500D, more preferably less than 300D (e.g. 50-300D) and more preferably 100 to 200D) and also preferably should be soluble in a liquid solvent or solvent mixture, most preferably in water or another physiologically tolerable solvent or solvent mixture.
  • the chemical shift, or even better the coupling constant of the nmr signal from the imaging nucleus in the MR imaging agent should preferably be influenced by physiological parameters (e.g. morphology, pH, metabolism, temperature, oxygen tension, calcium concentration, etc) .
  • physiological parameters e.g. morphology, pH, metabolism, temperature, oxygen tension, calcium concentration, etc.
  • influence by pH can be used as a general disease marker, whilst influence by metabolism may be a cancer marker.
  • the MR imaging agent may conveniently be a material which is transformed (e.g. at a rate such that its half life is no more than 10 x T 1 of the reporter nucleus, preferably no more than 1 x T x ) in the subject under study to a material in which the MR imaging nucleus has a different coupling constant or chemical shi t.
  • the subject may be inanimate or animate, e.g. a human or animal, a cell culture, a membrane-free culture, a chemical reaction medium, etc.
  • the reporter nucleus may provide information on the operation of the biochemical machinery of an organism where that machinery transforms the MR imaging agent and in so doing changes the chemical shift or coupling constant of the reporter nucleus.
  • the imaging process used in this case may be an nmr spectroscopic procedure rather than (or in addition to) an imaging procedure which generates a morphological image.
  • the MR imaging agent should preferably be 13 C or 15 N enriched, particularly preferably 13 C enriched.
  • Preferred MR imaging agents according to this aspect of the invention also exhibit the property of low toxicity.
  • the invention provides a water-soluble MR imaging agent compound:
  • a nucleus such as ] H, 13 C, 15 N or 29 Si, especially 13 C.
  • it also has some or all of the desired properties discussed earlier, e.g. solubility, paucity of other I ⁇ O nuclei (although these may be present in a counterion component of the compound if it is ionic) , solubility in water, etc .
  • Suitable MR imaging agents e.g. high T 1 agents, for use in the method of the invention involving spin refrigeration may contain nuclei such as protons.
  • nuclei such as protons.
  • other non- zero nuclear spin nuclei may be useful (e.g. 19 F, 3 i, 13 C, 15 N, 29 Si or 31 P, as well as : H) , preferably 1 E , 13 C, 15 N, 19 F, 29 Si and 31 P nuclei, with 13 C and iD N nuclei being particularly preferred.
  • the MR signals from which the image is generated may be substantially only from the MR imaging agent itself.
  • the polarised MR imaging agent may have a significant enough effect on in vivo protons for conventional X H-MRI to be carried out on those protons .
  • the MR imaging nucleus is other than a proton (e.g. 13 C or 15 N)
  • the natural abundance of 13 C and 15 N being negligible
  • image contrast will be advantageously high.
  • the method according to the invention has the benefit of being able to provide significant spatial weighting to a generated image.
  • the administration of a polarised MR imaging agent to a selected region of a sample means that the contrast effect may be localised to that region. The precise effect of course depends on the extent of biodistribution over the period in which the MR imaging agent remains significantly polarised.
  • specific body volumes i.e. regions of interest such as the vascular system or specific organs such as the brain, kidney, heart or liver
  • signal to noise particularly improved contrast to noise
  • a "native image" of the sample e.g. body
  • a "native image” may be generated to provide structural (e.g. anatomical) information upon which the image obtained in the method according to the invention may be superimposed.
  • a "native image” is generally not available where 13 C or 15 N is the imaging nucleus because of the low abundance of 13 C and lD N in the body.
  • a proton MR image may be taken to provide the anatomical information upon which the 13 C or 15 N image may be superimposed.
  • the MR imaging agent should of course be physiologically tolerable or be capable of being provided in a physiologically tolerable, administrable form where the sample is animate.
  • Preferred MR imaging agents are soluble in aqueous media (e.g. water) and are of course non-toxic where the intended end use is in vi vo .
  • the MR imaging agent once polarised will remain so for a period sufficiently long to allow the imaging procedure to be carried out in a comfortable time span.
  • sufficient polarisation will be retained by the MR imaging agent in its administrable form (e.g. in injection solution) if it has a T : value (at a field strength of 0.01-5T and a temperature in the range 20-40°C) of at least 5s, more preferably at least 10s, especially preferably 30s or longer, more especially preferably 70s or more, yet more especially preferably 100s or more (for example at 37°C in water at IT and a concentration of at least ImM) .
  • the MR imaging agent may be advantageously an agent with a long T : relaxation time.
  • the long T x relaxation time of certain 13 C nuclei is particularly advantageous and certain MR imaging agents containing 13 C nuclei are therefore preferred for use in the present method.
  • the ⁇ -factor of carbon is about % of the ⁇ _factor for hydrogen resulting in a armor frequency of about 10 MHz at 1 T .
  • the rf -absorption and reflections in a patient is consequently and advantageously less than in water (proton) imaging.
  • the signal-to-noise ratio is found to be independent of the MRI field strength when the corresponding frequency is higher than a few MHz.
  • the polarised MR imaging agent has an effective 13 C nuclear polarisation corresponding to the one obtained at thermal equilibrium at 300K in a field of 0.1T or more, more preferably 25T or more, particularly preferably 100T or more, especially preferably 5000T or more (for example 50 kT) .
  • the chemical shift effect When the electron cloud of a given molecule interacts with atoms in surrounding tissue, the shielding of the atom responsible for the the MR signal is changed giving rise to a shift in the MR frequency ("the chemical shift effect") .
  • the chemical shift will be changed and MR imaging agents in different chemical surroundings may be visualised separately using pulses sensitive to chemical shift.
  • the frequency difference between MR imaging molecules in different surroundings is 10 Hz or higher, preferably 20 Hz or higher, most preferably 150 Hz or higher (corresponding to 3.5ppm or higher)
  • the two components may be excited separately and visualised in two images. Standard chemical shift selective excitation pulses may then be utilised.
  • the frequency separation is less, the two components may not be separated by using frequency selective rf -pulses.
  • phase difference created during the time delay after the excitation pulse and before the detection of the MR signal may then be used to separate the two components.
  • Phase sensitive imaging pulse sequence methods (Dixon, Radiology, 1984, 153: 189-194 and Sepponen, Mag Res. Imaging, 3, 163-167, 1985) may be used to generate images visualising different chemcial surroundings or different metabolites.
  • the long T 2 relaxation time which may be a characteristic of a high T x agent will under these circumstances make it possible to use long echo times (TE) and still get a high signal-to-noise ratio.
  • TE long echo times
  • an important advantage of the MR imaging agents used in the present method is that they exhibit a chemical shift dependent on the local composition of the body in which they are localised.
  • Preferred MR imaging agents will exhibit a chemical shift of more than 2ppm, preferably more than lOppm depending on whether the MR imaging agent is localised inside or outside the vascular system. More preferred MR imaging agents will exhibit a chemical shift of more than 2 ppm, preferably more than 10 ppm, per 2 pH units or per Kelvin or upon being metabolised.
  • MR imaging agents containing polarised 13 C nuclei (or 15 N nuclei) exhibit large changes in chemical shift in response to physiological changes (e.g. pH, p0 2 , pC0 2 , redox potential, temperature or ionic concentrations of for example Na " , K + , Ca 2+ ) or metabolic activity and therefore may be used to monitor these parameters .
  • the T 2 valve may be sensitive to the physiological parameters of interest .
  • Solid MR imaging agents may exhibit very long , relaxation times and for this reason are especially preferred for use in the present method.
  • the T relaxation time may be several hours in the bulk phase, although this may be reduced by reduction of grain size and/or addition of paramagnetic impurities e.g. molecular oxygen.
  • the long relaxation time of solids advantageously allows the procedure to be conveniently carried out with less haste and is particularly advantageous in allowing the polarised solid MR imaging agent to be stored or transported prior to pharmaceutical formulation and administration.
  • the polarised MR imaging agent may be stored at low temperature and prior to administration, the MR imaging agent may be rapidly warmed to physiological temperatures using conventional techniques such as infrared or microwave radiation or simply by adding hot, sterile administrable media e.g. saline.
  • a polarised solid MR imaging agent is dissolved in administrable media (e.g. water or saline) , administered to a subject and conventional MR imaging performed.
  • administrable media e.g. water or saline
  • solid MR imaging agents are preferably rapidly soluble (e.g. water soluble) to assist in formulating administrable media.
  • the MR imaging agent should dissolve in a physiologically tolerable carrier (e.g. water or Ringers solution) to a concentration of at least ImM at a rate of lvriM/3 r T 1 or more, particularly preferably lmM/2T 1 or more, especially preferably lmM/T 1 or more.
  • the adminstrable medium may be heated, preferably to an extent such that the temperature of the medium after mixing is close to 37°C.
  • a polarised MR imaging agent may be administered (either alone or with additional components such as additional MR imaging agents) in liquid form.
  • the retention of polarisation in a liquid medium vis -a - vis a gas medium is significantly greater.
  • T 2 and T 2 are in general shorter for the liquid, the T 2 * effect due to diffusion is 10 5 times less significant for the liquid. Consequently for gaseous MR imaging agents the imaging sequence used generally has to be FLASH or GRASS while in contrast, more efficient imaging sequences may be used for liquids.
  • liquids generally have slower diffusion which makes it possible to use sequences such as echo planar imaging (EPI) .
  • EPI echo planar imaging
  • the overall technique will be faster and yield better resolution (voxel size ⁇ 1mm) than conventional techniques (voxel size approx. l-5mm) at current acquisition times. It will give good images at all fields including in low field (e.g. 0.01-0.5T) machines.
  • the hyperpolarised agent is stored (and/or transported) at low temperature and in an applied field as described above, since the method of the invention should be carried out within the time that the hyperpolarised solution of the MR imaging agent remains significantly polarised, it is desirable for administration of the polarised MR imaging agent to be effected rapidly and for the MR measurement to follow shortly thereafter.
  • the preferred administration route for the polarised MR imaging agent is parenteral e.g. by bolus injection, by intravenous, intraarterial or peroral injection.
  • the injection time should be equivalent to 5T X or less, preferably 3T X or less, more preferably T ⁇ or less, especially 0.1T 2 or less.
  • the lungs may be imaged by spray, e.g. by aerosol spray.
  • the MR imaging agent should be preferably enriched with nuclei (e.g. 15 N and/or 13 C nuclei) having a long T 1 relaxation time.
  • nuclei e.g. 15 N and/or 13 C nuclei
  • 13 C enriched MR imaging agents having 1 C at one particular position (or more than one particular position) in an amount in excess of the natural abundance, i.e. above about 1%.
  • Preferably such a single carbon position will have 5% or more 13 C, particularly preferably 10% or more, especially preferably 25% or more, more especially preferably 50% or more, even more preferably in excess of 99% (e.g. 99.9%) .
  • the ] X nuclei should preferably amount to >2% of all carbon atoms in the compound.
  • the MR imaging agent is preferably 1J C enriched at one or more carbonyl or quaternary carbon postions, given that a 13 C nucleus in a carbonyl group or in certain quaternary carbons may have a T 1 relaxation time typically of more than 2s, preferably more than 5s, especially preferably more than 30s.
  • the 13 C enriched compound should be deuterium labelled, especially adjacent the 1 C nucleus.
  • Preferred 13 C enriched compounds are those in which the 1J C nucleus is surrounded by one or more non-MR active nuclei such as O, S, C or a double bond.
  • Specifically preferred :3 C enriched agents are 13 C0 3 2" and H 13 C0 3 ⁇ (sodium salt for injection and calcium or potassium salt for polarisation) .
  • the invention provides a physiologically tolerable MR imaging composition
  • the composition is sterile and is stable at a physiologically temperature (e.g. at 10-40°C) .
  • the present invention provides the use of a paramagnetic substance for the manufacture of an MR imaging composition for use in a method of diagnosis involving generation of an MR image by MR imaging of a human or non-human animal body, wherein manufacture of said composition involves spin refrigeration nuclear spin polarisation of said MR imaging agent .
  • the invention provides the use of an MR imaging agent for the manufacture of an MR imaging composition for use in a method of diagnosis involving generation of an MR image by MR imaging of a human or non-human animal body, wherein manufacture of said composition involves spin refrigeration nuclear spin polarisation of said MR imaging agent .
  • the invention provides an MR imaging composition
  • the method of the invention should be carried out within the time that the MR imaging agent remains significantly polarised, once nuclear spin polarisation and dissolution has occurred, it is desirable for administration of the MR imaging agent to be effected rapidly and for the MR measurement to follow shortly thereafter.
  • the sample e.g. body or organ
  • the material should be transported to the relevant area, preferably at low temperature.
  • the preferred administration route for the MR imaging agent is parenteral, e.g. by bolus injection, by intravenous or intra-arterial injection or, where the lungs are to be imaged, by spray, e.g. by aerosol spray. Oral and rectal administration may also be used.
  • the method according to the invention has the benefit of being able to provide significant spatial weighting to a generated image.
  • the administration of a polarised MR imaging agent to a selected region of a sample means that the contrast effect is, in general, localised to that region.
  • the precise effect depends on the extent of biodistribution over the period in which the MR imaging agent remains significantly polarised.
  • specific body volumes i.e. regions of interest such as the vascular system into which the MR imaging agent is administered may be defined with improved signal to noise properties of the resulting images in these volumes.
  • the ⁇ -factor of carbon is about % of the ⁇ _factor for hydrogen resulting in a Larmor frequency of about 10 MHz at 1 T .
  • the rf-absorption in a patient is consequently and advantageously less than in 1 U imaging.
  • a further advantage of MR imaging agents containing polarised 13 C nuclei is the ability to utilise large changes in chemical shift in response to physiological changes, e.g. pH or temperature.
  • the MR imaging agent may be conveniently formulated with conventional pharmaceutical or veterinary carriers or excipients.
  • MR imaging agent formulations manufactured or used according to this invention may contain, besides the MR imaging agent, formulation aids such as are conventional for therapeutic and diagnostic compositions in human or veterinary medicine but will be clean, sterile and free of paramagnetic, superparamagnetic, ferromagnetic or ferrimagnetic contaminants.
  • the formulation may for example include stabilizers, antioxidants , osmolality adjusting agents, solubilizing agents, emulsifiers, viscosity enhancers, buffers, etc.
  • none of such formulation aids will be paramagnetic, superparamagnetic, ferromagnetic or ferrimagnetic .
  • the formulation may be in forms suitable for parenteral (e.g. intravenous or intraarterial) or enteral (e.g. oral or rectal) application, for example for application directly into body cavities having external voidance ducts (such as the lungs, the gastrointestinal tract, the bladder and the uterus), or for injection or infusion into the cardiovascular system.
  • parenteral e.g. intravenous or intraarterial
  • enteral e.g. oral or rectal
  • solutions, suspensions and dispersions in physiological tolerable carriers e.g. water
  • physiological tolerable carriers e.g. water
  • the formulation which preferably will be substantially isotonic, may conveniently be administered at a concentration sufficient to yield a 1 micromolar to 1M concentration of the MR imaging agent in the imaging zone; however the precise concentration and dosage will of course depend upon a range of factors such as toxicity, the organ targeting ability of the MR imaging agent, and the administration route.
  • the optimum concentration for the MR imaging agent represents a balance between various factors. In general, optimum concentrations would in most cases lie in the range 0. ImM to 10M, especially 0.2mM to IM, more especially 0.5 to 500mM.
  • Formulations for intravenous or intraarterial administration would preferably contain the MR imaging agent in concentrations of lOmM to 10M, especially 50mM to 500 mM.
  • concentration may conveniently be 0. ImM to 10M, preferably 0.2mM to 10M, more preferably 0.5mM to IM, still more preferably 1.
  • Parenterally administrable forms should of course be sterile and free from physiologically unacceptable agents and from paramagnetic, superparamagnetic, ferromagnetic or ferrimagnetic contaminants, and should have low osmolality to minimize irritation or other adverse effects upon administration and thus the formulation should preferably be isotonic or slightly hypertonic.
  • Suitable vehicles include aqueous vehicles customarily used for administering parenteral solutions such as Sodium Chloride solution, Ringer's solution, Dextrose solution, Dextrose and Sodium Chloride solution, Lactated Ringer's solution and other solutions such as are described in Remington's Pharmaceutical Sciences, 15th ed., Easton: Mack Publishing Co., pp.
  • compositions can contain preservatives, antimicrobial agents, buffers and antioxidants conventionally used for parenteral solutions, excipients and other additives which are compatible with the MR imaging agents and which will not interfere with the manufacture, storage or use of the products .
  • Intra-arterial injection is useful for preparing angiograms and intravenous injection for imaging larger arteries and the vascular tree.
  • the dosages of the MR imaging agent used according to the method of the present invention will vary according to the precise nature of the MR imaging agents used, of the tissue or organ of interest and of the measuring apparatus. Preferably the dosage should be kept as low as possible whilst still achieving a detectable contrast effect. Typically the dosage will be approximately 10% of LD 50 , eg in the range 1 to lOOOmg/ kg, preferably 2 to 500mg/kg, especially 3 to 300mg/kg.
  • the invention provides an apparatus for use in the method described herein, the apparatus comprising: i) a chamber cooled by, e.g. liquid helium, to a temperature preferably lower than 80K, more preferably lower than 20K, even more preferably lower than 4.2K, most preferably lower than or equal to IK, disposed in the primary magnetic field of MR apparatus, or in a separate magnetic field, of strength 0.2T or more, preferably 0.5 to 10T; and wherein said chamber is: i) adapted to receive particulate solid MR imaging agent, doped with or intimately mixed with paramagnetic polarising agent; ii) rotates said agent about an axis non-parallel with the primary field or passes said agent through a conduit such that it rotates in that way (e.g.
  • a spiral or helical conduit or mixes said agent (e.g. by means of rotating paddles) such that it rotates in that way, or (where the chamber is in a separate magnetic field) rotates the magnetic field about one or more axes ; iii) dissolves said polarised solid agent in or passes it to a mixing chamber, where it is dissolved in a physiologically tolerable solvent; iv) passes the solution thus formed through or over an immobilised paramagnetic metal binding agent (e.g. an ion exchange resin) and/or through a filter; v) and into the conduit for administration into a sample (e.g. a patient) situated within the primary magnetic field of the MR imager.
  • an immobilised paramagnetic metal binding agent e.g. an ion exchange resin
  • hyperpolarisation of the solid MR imaging agent is effected by increasing the polarisation of the nucleus in said agent to be observed in said MR investigation by polarisation transfer from paramagnetic electron spins with large anisotropy factors. It is envisaged that, in the method according to the invention, the level of polarisation achieved should be sufficient to allow the hyperpolarised solution of the MR imaging agent to achieve a diagnostically effective contrast enhancement in the sample to which it is subsequently administered in whatever form.
  • a degree of polarisation which is at least a factor of 2 or more above the equilibrium value at the temperature and the magnetic field in which MRI is performed, preferably a factor of 10 or more, particularly preferably 100 or more and especially preferably 1000 or more, e.g. 50000.
  • Figure 1 is a schematic diagram showing the interactions between the electronic singlet and triplet states of a photoactive molecule
  • Figure 2 shows the solid effect in its pure form
  • Figure 3 shows the differential solid effect
  • Figure 4 shows the energy levels of Ni 2+ in sapphire when the c-axis is parallel to the field direction
  • Figure 5 shows the energy levels of Ni 2+ in sapphire when the c-axis is perpendicular to the field direction.
  • a sample of a compound to be nuclear spin polarised is placed in a sample holder with transparent, preferably quartz, walls.
  • a material that absorbs light and prevents the passage of light past the centre of the sample Preferably it is a rod or tube of oxidized copper or silver or other dark material with good heat conduction properties.
  • the charged sample holder is placed in a cooling bath, containing liquid nitrogen or helium, equipped with windows to allow for the passage of two light beams converging on the sample. This cooling bath is located in a magnetic field, of strength between 0.01 to 10 Tesla depending on the relaxation characteristics of the sample.
  • the sample is then irradiated with light from two different sources.
  • Source one is a low power light source with a wavelength chosen to excite molecules from the S c state to one of the higher S- states .
  • the desired wavelength is selected with a monochromator or a suitable combination of filters.
  • the light source is typically a mercury lamp.
  • the irradiation power is chosen to give a substantial degree of hole burning in the chosen transition.
  • this light source may operate in a pulsed fashion.
  • Source two is a high power light source with polariser and quarter wave plate so that a circularly polarised light is obtained.
  • the wavelength is chosen to excite molecules in the T 2 state to the T 2 state. This wavelength is typically longer than the S 0 -S n wavelength.
  • the power should be the highest possible compatible with the cooling capacity.
  • the sample thickness is adjusted so that this light penetrates the whole sample.
  • the sample is rotated, typically with a frequency of 1 to 100 Hz. After an irradiation time of 5 times the nuclear T 2 , a maximum polarisation has been reached and the sample is rapidly removed from the cooling bath and poured into warm (40°C), agitated water (optionally with pharmacological additives) . It is important to keep the sample within the magnetic field during this operation and until the solids have been dissolved.
  • the solid is nuclear spin polarised in microcrystallic or amorphous powder form, optionally agitated by a gas (e.g. He) whereby to produce a "dust-in-air suspension" .
  • a gas e.g. He
  • aqueous solution is rapidly transferred to an NMR spectrometer and a spectrum with enhanced intensity is recorded.
  • aqueous solution is rapidly injected into a rat, which is placed in an MRI- scanner, and a picture with enhanced contrast and intensity is recorded.
  • a substrate with long T ⁇ times e.g. a 13 C or 15 N-labelled compound, is milled with anisotropic metal ions.
  • the mixture formed is placed in a sample holder and immersed in liquid helium in a IT magnet.
  • a vacuum is applied to the helium bath and the sample holder is spun at 100 Hz around the axis of which is perpendicular to the external magnetic field. After several minutes the vacuum is released and the sample is rapidly removed and poured into water at 40°C.
  • the solution thus formed is rapidly passed through an ion-exchange column to remove the anisotropic metal ions and is then ready for injection, optionally with the addition of pharmacological additives.

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  • High Energy & Nuclear Physics (AREA)
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Abstract

L'invention porte sur un procédé d'examen par résonance magnétique d'un échantillon, de préférence de corps humain ou animal, comportant les étapes suivantes: (i) polarisation du spin nucléaire d'un agent solide d'imagerie par RMN (par exemple d'un matériau dont la structure moléculaire contient des noyaux à spin nucléaire non nul), soit (a), par réfrigération du spin, soit (b), par irradiation par de la lumière à polarisation circulaire; (ii) administration audit échantillon de l'agent d'imagerie par RMN de préférence après dissolution dans un solvant physiologiquement tolérable, et également, de préférence, après séparation d'avec tout ou partie des substances paramagnétiques ou des photophores; (iii) soumission dudit échantillon à un rayonnement d'une fréquence choisie pour exciter les transitions des spin nucléaires dans les noyaux sélectionnés, par exemple les noyaux à spin polarisé de l'agent d'imagerie; (iv) détection des signaux provenant de l'échantillon; et (v) facultativement production d'une image, de données dynamiques sur les flux, de données de diffusion, de données de perfusion, de données physiologiques (par exemple sur pH, pO2, pCO2, la température, ou les concentrations en ions), ou de données sur le métabolisme, extraites des signaux détectés.
PCT/GB2000/001888 1999-05-19 2000-05-17 Procede d'imagerie par rmn utilisant des solutions d'agents de contraste provenant de la dissolution de materiaux hyperpolarises WO2000072031A1 (fr)

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GB0126355A GB2364785B (en) 1999-05-19 2000-05-17 Methods of magnetic resonance imaging (MRI) using contract agent solutions formed from the dissolution of hyperpolarised materials
US09/990,512 US20020058869A1 (en) 1999-05-19 2001-11-16 Methods of magnetic resonance imaging (MRI) using contract agent solutions formed from the dissolution of hyperpolarised materials

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WO2002036005A1 (fr) * 2000-11-03 2002-05-10 Amersham Health As Procedes et dispositifs destines a des echantillons rmn polarises
WO2002086478A2 (fr) * 2001-04-23 2002-10-31 Metabometrix Limited Procedes d'analyse de donnees spectrales et leurs applications
DE10259793A1 (de) * 2002-12-19 2004-07-22 Siemens Ag Verfahren zur Bildgebung eines Stoffwechselvorgangs eines Lebewesens
US7901873B2 (en) 2001-04-23 2011-03-08 Tcp Innovations Limited Methods for the diagnosis and treatment of bone disorders
CN105785478A (zh) * 2016-04-13 2016-07-20 华中科技大学 一种适用于测试固相试样与供电电极之间面极化效应的系统
CN109521038A (zh) * 2018-11-30 2019-03-26 华东师范大学 一种基于磁共振核自旋单态选择性检测多巴胺的方法

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Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002036005A1 (fr) * 2000-11-03 2002-05-10 Amersham Health As Procedes et dispositifs destines a des echantillons rmn polarises
US7102354B2 (en) * 2000-11-03 2006-09-05 Amersham Health As Methods and devices for hyperpolarising and melting NMR samples in a cryostat
WO2002086478A2 (fr) * 2001-04-23 2002-10-31 Metabometrix Limited Procedes d'analyse de donnees spectrales et leurs applications
WO2002086478A3 (fr) * 2001-04-23 2003-04-10 Metabometrix Ltd Procedes d'analyse de donnees spectrales et leurs applications
US7901873B2 (en) 2001-04-23 2011-03-08 Tcp Innovations Limited Methods for the diagnosis and treatment of bone disorders
DE10259793A1 (de) * 2002-12-19 2004-07-22 Siemens Ag Verfahren zur Bildgebung eines Stoffwechselvorgangs eines Lebewesens
DE10259793B4 (de) * 2002-12-19 2009-10-15 Siemens Ag Verfahren zur Bildgebung eines Stoffwechselvorgangs eines Lebewesens
CN105785478A (zh) * 2016-04-13 2016-07-20 华中科技大学 一种适用于测试固相试样与供电电极之间面极化效应的系统
CN105785478B (zh) * 2016-04-13 2018-02-02 华中科技大学 一种适用于测试固相试样与供电电极之间面极化效应的系统
CN109521038A (zh) * 2018-11-30 2019-03-26 华东师范大学 一种基于磁共振核自旋单态选择性检测多巴胺的方法

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