Metal biosensors based on compounds with metal-sensitive chemical shifts for magnetic resonance spectroscopy and imaging and their uses

The present invention relates to the use of compounds with at least one metal-sensitive chemical shift for determining metal concentrations and/or measuring metal concentration changes, by quantifying the NMR signal corresponding to said metal-specific chemical shift, preferably its intensity, frequency and/or bandwidth, wherein the compound is selected from the group of pyro-EGTA, EGTA, EDTA, AATA, APTRA, BAPTA, HIDA, citrate, CarboxyGlutamate (CGlu), arylazo chromotopic acid, beta-diketone (crown-ether), mono-, di- , or tri-pyridyl aniline, mono-, di-, or tri-pyridyl amine, trimethylphenylammonium, or derivatives thereof. The present invention relates to the use of said compounds with at least one metal-sensitive chemical shift for detecting metals qualitatively. The present invention further relates to biosensors comprising at least one of the compounds of the present invention together with one or several further components selected from pharmaceutically acceptable earners, moieties interacting with biological targets and/or pharmaceutically acceptable excipients. The present invention also relates to the use of the compounds for diagnosing and/or monitoring treatment of a disease causing changes in metal concentrations. The present invention is furthermore related to in vitro and in vivo methods for determining metal concentration and/or measuring metal concentration changes using the compounds or biosensors. The present invention also relates to methods of diagnosing and/or monitoring treatment of a disease causing changes in metal concentrations wherein the compounds or biosensors are applied. The present invention also relates to use of the compounds or biosensors in quality control of food or in the examination of plants and organisms or for monitoring of environmental resources. The present invention further relates to novel derivatives of pyro-EGTA, EGTA, EDTA, AATA, APTRA and BAPTA as well as their uses.

BACKGROUND OF THE INVENTION

Metal ions are of fundamental importance for biological processes since they function as essential constituents of structural proteins and enzymes, or as signaling molecules and second messengers. The most prominent example of the last category is calcium, which is important in many signal-transduction cascades and also essential for the signaling in electrically excitable cells, in particular the electrochemical conversion at the presynaptic synapses of neurons mediated through voltage gated influx and intracellular release of calcium as a function of membrane potential. Organ(ism)s thus have to tightly control the concentration of metals and their spatiotemporal distribution as many factors including e.g. increased metabolic demand, malnutrition or contact with toxic concentrations of metals present for instance in environmental pollutants can cause deflections from the physiological range.

Synthetic metal sensors are available for optical readouts based on absorbance (Durham et al. , 1983) and fluorescence (Carter et al , 2014). There also exist genetically encoded sensors for readout via fluorescence (Looger et al, 2013) and bioluminescence (in conjunction with appropriate synthetic substrates). These photon-dependent metal sensors however all suffer from the poor penetration of photons in biological tissue or in opaque and/or turbid samples. The penetration depth depends on the specific method and desired resolution; even optimal use of near-infrared illumination and independence scattering as achieved by optacoustics however still limits the maximum penetration depth in biological tissues to a few centimeters (Ntziachristos et al, 2010). For these photon-dependent imaging methods to measure deeper structures in vivo, invasive methods are necessary that e.g. surgically insert optical guides such as fiber bundles into tissue. For diagnostic measurements of in vitro or ex-vivo samples (such as biological fluids and tissue as well also non-medical samples such as waste water) photon-dependent methods are also severely limited in their performance by the samples' opacity and turbidity.

It would therefore be of great value for biomedical diagnostics as well as for applications in food and environmental testing if robust photon-independent detection of metals in opaque and turbid media and non-invasive in vivo imaging of their distribution in organ(ism)s could be achieved at sub-millimeter resolution.

One non-invasive photon-independent method that fulfills these criteria is nuclear Magnetic Resonance Imaging (MRI) that routinely achieves whole-body coverage in humans. Metal- sensitive contrast agents for NMR and MRI have been developed previously. They fall into four categories according to their physical mechanism: T ₂ relaxation agents, Tj relaxation agents, CEST agents and chemical shift agents. A first category of metal-sensitive contrast agents consists of (super)paramagnetic nanoparticles in the case that they consist of iron-oxide abbreviated SPIOs, which mainly give rise to so-called T ₂ or T ₂ * contrast in appropriate MRI sequences. A change in the agglomeration state of SPIOS alters their T ₂ /T ₂ * contrast (Perez et al , 2002), an effect that can be made specific to analytes of interest via surface modifications with appropriate affinities for the analytes. Using peptide and protein surface modifications, this effect was used to generate SPIOs that exhibited calcium-dependent agglomeration and accompanying T ₂ signal changes (Atanasijevic et al , 2006). T ₂ sensors can give contrast at nanomolar concentrations (Shapiro et al. , 2006) and metal-dependent contrast changes can be a few fold. Due to their large size though, these agents are very difficult to deliver to tissues. In addition, their response time is only on the order of a few seconds and a function of their concentration due to the complicated agglomeration process (Shapiro et al , 2006). In addition, there are data which show that after degradation of SIPOs nanostructure, the iron is metabolized by the organism, one of the reasons why the U.S. Food and Drug Administration has approved some SPIOs for imaging of humans under certain conditions. However, there remain concerns about the biosafety of SPIOs such that a potential use for e.g. neuroimaging is off-label (Winer et al , 2012). Whereas the agglomeration-based T ₂ contrast mechanism using SPIOs agent is used for in v tro-diagnostics {e.g. by the company T2 Biosystems), successful in vivo use has not been demonstrated probably due to the difficulties in preventing unspecific agglomeration events and control delivery and stoichiometry in the target tissue.

A second category of sensors generates metal-dependent MRI contrast changes by altering the so-called Ti spin-lattice through modulating access of protons to a macrocycle-coordinated metal (in most cases a lanthanide) as a function of metal binding. With respect to analytes, calcium, magnesium, zinc, iron and potassium have been targeted, but the maximum relaxivity changes of any of these relaxation agents was only a factor of two to three with most of these contrast agents exhibiting much smaller signal changes (Que et al. , 2010). Toxic metals such as cadmium and nickel or lead have not been targeted with NMR-based metal sensors so far. Because of the low sensitivity of proton MRI and the low relaxivity of lanthanide-based MRI contrast agents, these contrast agents have to be used at concentrations of hundreds of micromolar (Caravan et al , 2006) and even higher concentrations for chemical shift agents that rely on the natural abundance of heteronuclei. This low signal can only be compensated for by long examination times and spatial averaging which compromises spatial and temporal resolution to a degree that is not practical for imaging application in preclinical animal models or small specimens. For clinical applications in human subjects, long radiofrequency irradiation is also limited by the allowed specific absorption rate (SAR). Furthermore, a concern for the (pre)clinical use of gadolinum-complexes is their potential toxicity, which may cause severe syndromes such as nephrogenic systemic fibrosis.

A third category of metal-sensitive MRI contrast agents are not based on relaxation rate changes but rely on the detection of chemical shift, which are changes of the nuclear spin frequency due to changes (relative to some standard such as tetramethylsilane (TMS)) of the microenvironment that the respective nucleus is affected by. ¹⁹ F containing moieties based on the calcium chelators BAPTA and Quin2 have been generated (Smith et al, 1983; Steenbergen et al, 1987; Schanne et al, 1990) ; in particular, the 5,5'-difluoro derivative (5F- BAPTA) exhibits robust enough chemical shifts. With this system, the identity of the chelated metal was not obtained from the NMR signal and can only be inferred from the selectivity of the chelator, in this case BAPTA. Also US 2006/0193781 Al, which describes a method of magnetic resonance imaging (MRI) for in vivo mapping of concentration of a target metal ion in tissue, discloses the use of 5F-BAPTA and 5T-BAPTA agents. In Robitaille et al (1992) the divalent metal chelator, AATA is described that was modified with tetra ¹³ C (-

13

CH ₂ COOH and a chemical shift was measured via Proton-observed carbon-edited (POCE) NMR spectroscopy.

A fourth category of MRI metal sensors are based on so-called chemical exchange saturation transfer (CEST), i.e. the selective saturation of the magnetization of a pool of nuclei (e.g. protons) associated with the CEST contrast agent and observation of the signal change due to chemical exchange with that pool. The fluorinated BAPTA derivative 5F-BAPTA was used in CEST mode to enhance the sensitivity to detect calcium (Bar-Shir et al.) and was recently extended with a molecule that was also fluorinated at the 4 position (5,5', 6,6'-tetrafluoro- BAPTA) that can also detect zinc and iron (Bar-Shir et al , 2014). Angelovski et al. (2011) have developed an agent for calcium in which a paramagnetic gadolinium enhances the CEST effect (PARACEST). Both of these methods however require micromolar concentrations of the CEST agent and the temporal resolution of the CEST method is generally slower than for relaxation agents due to the duration of saturation pulses. In brief, the above-mentioned methods all suffer from a lack of sensitivity, obviously one of the major obstacles for in vivo MRI in general, necessitating the use of higher micromolar if not millimolar concentrations of the contrast agent.

To improve MRFs sensitivity, several so-called hyperpolarization methods have been developed that can increase the polarization of nuclear spins and thus the available signal (Viale et al. 2009, Viale et al. 2010). In the case of the noble gases helium ( He) and xenon

( Xe), hyperpolarization can be achieved via optical pumping. In case the contrast agent of interest can be generated through hydrogenation reaction, Para-Hydrogen Induced Polarization (PHIP) can be employed.

Another fairly general method for hyperpolarization is Dynamic Nuclear Polarization (DNP) which is based on the transfer of spin polarization from electrons to nuclei. This can be achieved by radiofrequency irradiation of the compound together with a radical at low temperatures with radiofrequency near the electron resonance frequency. The resultant increase in signal of up to several orders of magnitude allows the measurement of insensitive nuclei such as ^I3 C (Ardenkjaer-Larsen et al, 2003). These nuclei may be contained in hyperpolarizable small contrast agent compounds, which may be indistinguishable from endogenous molecules by the biochemical processes of interest and are thus also probably non-toxic. A prominent example of this approach is hyperpolarized [l- ¹³ C]-pyruvate that can be used to map the distribution of the enzyme lactate dehydrogenase (LDH) via detecting the chemical shifts occurring upon conversion of pyruvate to lactate. This can for instance be useful for the spatiotemporal detection of tumor cells that may exhibit pathological LDH activity as may be the case for prostate carcinoma (Nelson et al , 2013 -1 and Nelson et al ,

89

2013 -2). A DNP -hyperpolarized molecule based on Y has been described that shows a pH- dependent chemical shift (Jindal et al , 2010).

Nonaka et al. (2013) have recently published a ¹⁵ N-containing compound, namely [ ¹⁵ N, Dpjtrimethylphenylammonium ([ ¹⁵ N, DgJTMPA) that can be hyperpolarized by DNP and exhibits a chemical shift of the ¹⁵ N moiety when incorporated to the metal chelator APTRA. However, there is no demonstration in this work that the chemical shifts are specific to the metals that are coordinated.

In summary, there is a need in the art of improved means and methods for measuring metal concentration changes, preferably with spatial resolution and in real time in a photon- independent fashion in vitro, ex vivo and especially non-invasively in vivo. For the latter, a method that can simultaneously and specifically and robustly detect several metals at an increased sensitivity is needed.

SUMMARY OF THE INVENTION

According to the present invention this object is solved by the of a compound with at least one metal-sensitive chemical shift for determining metal concentrations and/or measuring metal concentration changes,

by quantifying the NMR signal corresponding to said metal-specific chemical shift, preferably its intensity, frequency and/or bandwidth,

wherein the compound is selected from the group of:

pyro-EGTA,

EGTA,

EDTA,

AATA,

APTRA,

BAPTA,

HIDA,

citrate,

carboxyglutamate (CGlu),

or derivatives thereof; arylazo chromotopic acid derivatives,

beta-diketone (crown-ether) derivatives,

mono-, di-, or tri-pyridyl aniline derivatives,

mono-, di-, or tri-pyridyl amine derivatives,

trimethylphenylammonium derivatives . and the hydrates, salts, solutions, stereoisomers of these compounds and derivatives.

According to the present invention this object is solved by a biosensor for determining metal concentrations and/or measuring metal concentration changes, comprising (i) at least one compound with at least one metal-sensitive chemical shift of the present invention,

(ii) one or several pharmaceutically acceptable carriers, moieties interacting with biological targets and/or excipients,

(iii) optionally, a reference compound.

According to the present invention this object is solved by providing the compound of the present invention or the biosensor of the present invention for use in in vivo magnetic resonance imaging (MRI) or magnetic resonance spectroscopy (MRS) with optional multimodal detection of additional label(s) via absorbance/transmission, reflection, fluorescence or optoacoustic or ultrasound measurements and imaging.

According to the present invention this object is solved by providing the compound of the present invention or the biosensor of the present invention for use in diagnosing and/or monitoring treatment of diseases causing changes in metal concentrations,

According to the present invention this object is solved by the use of the compound of the present invention as metal sensor for in vitro or ex-vivo NMR spectroscopy.

According to the present invention this object is solved by an in vitro method for determining metal concentration and/or measuring metal concentration changes, comprising the steps of

(i) providing a sample,

(ii) adding a compound with at least one metal-sensitive chemical of the present invention or the biosensor of the present invention to the sample,

wherein the compound or biosensor has been hyperpolarized and/or resolved, (iii)

magnetic resonance imaging (MRI), nuclear magnetic resonance (NMR) spectroscopy or magnetic resonance spectroscopy imaging (MRSI) and thereby determining the spatial distribution of metal concentration or metal concentration changes of or in the sample

(1) by obtaining a chemical shift difference between at least one metal-sensitive chemical shift of the compound and a metal-independent chemical shift, such metal- independent chemical shift acting as a reference chemical shift, or

(2) by measurement of the absolute chemical shift, or

(3) by measuring chemical shift differences involving at least one metal-sensitive shift, optionally, by obtaining additional measurements of metal-insensitive signals that relate to the concentration of said compound or biosensor of the present invention, for instance based on radioactivity, absorbance, fluorescence, optoacoustic or ultrasound signal from said compound or biosensor of the present invention containing the appropriate radioactive moiety, fluorophore/chromophore.

According to the present invention this object is solved by an in vivo method for determining metal and/or measuring metal concentration changes, preferably in real-time, comprising the steps of

(i) applying or administering a compound with at least one metal-sensitive chemical shift of the present invention or a biosensor of the present invention to the body of a patient or non- human animal,

wherein the compound or biosensor has been hyperpolarized and/or resolved,

(ii) performing magnetic resonance imaging (MRI) and thereby determining one or several metal concentrations or metal concentration changes of or in the body of said patient or non-human animal

(1) by correcting a spatiotemporally resolved metal-sensitive signal for differences in local and time-dependent signal intensities, e.g. due to differences in the local concentration of the metal sensors, and

by obtaining the chemical shift and/or its integrated peak area and/or peak amplitude from at least one metal-sensitive chemical shift and a metal-insensitive reference in the form chemical shift and/or integrated peak area from at least one metal-insensitive chemical shift or a function of metal-sensitive shifts,

or

(2) by measurement of the absolute chemical shift, integrated peak area or peak amplitude,

wherein the reference signal is obtained

by measuring a metal-insensitive MRI signal from another nucleus such as proton via a lanthanide, ¾ ¹³ C, ¹⁵ N, ⁱ⁹ F, ²⁹ Si, ³¹ P and/or ⁸⁹ Y, or

by combination with another method, such as a PET measurement, or fluorescence or optoacoustics or ultrasound. According to the present invention this object is solved by a method of diagnosing and/or monitoring treatment of a disease causing changes in metal concentrations, comprising the steps of

(i) applying or administering a compound with at least one metal-sensitive chemical shift of the present invention or a biosensor of the present invention to the body of a patient or non- human animal,

wherein the compound or biosensor has been hyperpolarized and/or resolved,

(ii) performing magnetic resonance imaging (MRI) or magnetic resonance spectroscopy (MRS) and thereby determining one or several metal concentrations or metal concentration changes of or in the body of said patient or non-human animal

(1) by obtaining over time the chemical shift and/or its integrated peak area and/or its peak amplitude from at least one metal-sensitive chemical shift and a metal- insensitive reference in the form of a chemical shift and/or its integrated peak area and/or peak amplitude from at least one metal-insensitive chemical shift or a function of metal-sensitive shifts,

or

(2) by measurement of the absolute chemical shift, integrated peak area or peak amplitude,

wherein the reference signal is obtained

by measuring a metal-insensitive MRI signal from another nucleus such as proton via a lanthanide, 1H, ¹³ C, ¹⁵ N, ^{I 9} F, ²⁹ Si, ^3, P and/or ⁸⁹ Y, or

by combination with another method, such as a PET measurement, or fluorescence or optoacoustics or ultrasound,

(iii) calculating metal concentration maps based on spatially resolved metal concentration values or metal concentration changes determined in step (ii).

According to the present invention this object is solved by the use of the compound of the present invention or the biosensor of the present invention in quality control of food or in the examination of plants and organisms, or for monitoring of environmental resources with respect to pollution and harmful metal concentrations.

According to the present invention this object is solved by a derivative or analog of pyro- EGTA, AATA, APTRA or BAPTA, comprising metal affinity modifying moiety /moieties, wherein the metal affinity modifying moiety/moieties is/are selected from halogen (e.g. CI, Br, I), a hyperpolarizable nucleus (e.g. ¹³ C, ¹⁹ F, or ³¹ P, ²⁹ Si, ¹⁵ N) or NH ₂ .

According to the present invention this object is solved by a derivative or analog of EDTA, EGTA, comprising one or more hyperpolarizable nuclei, which is/are positioned close to the metal-coordinating moieties such that a metal-specific chemical shift can be obtained.

According to the present invention tins object is solved by using the derivative or analog of pyro-EGTA, AATA, APTRA or BAPTA of the present invention or the derivative or analog of EDTA or EGTA of the present invention for the uses and in the methods according to the present invention.

DESCRIPTION OF THE PREFERRED EMBODIMENTS OF THE INVENTION

Before the present invention is described in more detail below, it is to be understood that this invention is not limited to the particular methodology, protocols and reagents described herein as these may vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to limit the scope of the present invention which will be limited only by the appended claims. Unless defined otherwise, all technical and scientific terms used herein have the same meanings as commonly understood by one of ordinary skill in the art. For the purpose of the present invention, all references cited herein are incorporated by reference in their entireties.

Metal biosensors based on metal chelators with metal-sensitive chemical shift (s)

As discussed above, the present invention provides the use of a compound with at least one metal-sensitive chemical shift for determining metal concentrations and/or measuring metal concentration changes.

In particular, the present invention provides the use of a compound with at least one metal- sensitive chemical shift for detecting metals qualitatively or for determining metal concentrations and/or measuring metal concentration changes,

by quantifying the NMR signal corresponding to said metal-specific chemical shift, preferably its intensity, frequency and/or bandwidth. Preferably, for detecting metals qualitatively or quantitatively, the intensity, frequency and/or bandwidth of the NMR signal corresponding to the metal-specific chemical shift is compared with reference sample(s). Preferably, the hyperpolarizable nuclei of the compound are hyperpolarized.

Current NMR-based metal sensors fail to solve the objectives of the present invention due to a combination of their low Signal-to-Noise Ratio (SNR) and limitation by SAR, potential toxicity and difficulties of delivery to the tissue of interest. Current NMR-based metal sensors have thus not emerged as robust tools for in vitro, ex vivo or in vivo use in preclinical animal models and it is unlikely that these methods will translate into the clinic or biomedical research for use in humans.

The inventors have now found that it is possible to make use of the metal-specific displacement of chemical shifts in compounds for determining one or several metal concentrations and/or measuring metal concentration changes. In particular, this concerns the displacement of

metal-sensitive 1H chemical shifts in Ή-magnetic resonance imaging and/or Ή magnetic resonance spectroscopy, and/or

metal-sensitive C chemical shifts in C-magnetic resonance imaging and/or C magnetic resonance spectroscopy, and/or

metal-sensitive ¹⁵ N chemical shifts in ¹⁵ N-magnetic resonance imaging and/or ^l3 N magnetic resonance spectroscopy, and/or

metal-sensitive ¹⁹ F chemical shifts in ^I9 F-magnetic resonance imaging and/or ¹⁹ F magnetic resonance spectroscopy, and/or

metal-sensitive ²⁹ Si chemical shifts in ²⁹ Si-magnetic resonance imaging and/or ²⁹ Si magnetic resonance spectroscopy, and/or

metal-sensitive ^3, P chemical shifts in ^jl P-magnetic resonance imaging and/or ^3l P magnetic resonance spectroscopy, and/or

metal-sensitive ⁸⁹ Y chemical shifts in ⁸⁹ Y-magnetic resonance imaging and/or ⁸⁹ Y magnetic resonance spectroscopy.

Preferably, a compound with at least one metal-sensitive chemical shift is ^-labelled, ^R elabelled, ^{] 5} N-labelled, ¹⁹ F-labelled, ²⁹ Si-labelled, ^3I P-labelled, and/or ⁸⁹ Y-labelled. As used herein "chemical shift" refers to a small change in the spin frequency of a nucleus due to its microenvironment with respect to a reference frequency of a suitable standard, such as tetramethylsilane (TMS). Chemical shift is commonly expressed in parts-per-million (ppm).

The term "displacement of a chemical shift", as used herein is meant to refer to a change in position of the respective chemical shift. In this context, "displacement of a chemical shift" is preferably meant to refer to a change in position of a Ή, ¹³ C, ¹⁵ N, ¹⁹ F, ²⁹ Si, ³¹ P and ⁸⁹ Y chemical shift. The measure of metal -concentration can derive from the displacement of a chemical shift and/or from the integrated area of a displaced chemical shift and/or from peak amplitude of a displaced chemical shift.

Preferably, a compound with at least one metal-sensitive chemical shift comprises one or more metal-sensitive chemical shifts (namely one or more metal-sensitive 1H and/or ¹³ C and/or ¹⁵ N and/or ¹⁹ F and/or ²⁹ Si and/or ³¹ P and/or ⁸⁹ Y chemical shifts), such as two, three, four or more.

Here, a novel series of metal-biosensors is presented (based on several classes of metal chelators, such as pyro-EGTA, EGTA, EDTA, AATA, APTRA, BAPTA, HIDA, citrate, carboxyglutamate (CGlu), arylazo chromotopic acid, beta-diketone (crown-ether), mono/di/tri-pyridyl aniline or mono/di/tri-pyridyl amine, trimethylphenyl ammonium, incorporating one or more hyperpolarizable isotopes) for magnetic resonance measurements that are sensitive and specific to various metals in concentration ranges relevant for detection of deviations from the physiological range.

As used herein "magnetic resonance" refers to the observation of Larmor precession in a magnetic field (see Ernst, 1997 and de Graaf, 2007), and includes measurements at a NMR spectrometer, an NMR microimaging system, an MRJ scanner, a low-field NMR device, microfluidic arrays ("NMR on a chip"), and/or combinations thereof. Measurement includes all variations of spatially and/or spectrally resolved magnetic resonance techniques, such as magnetic resonance spectroscopy (MRS), magnetic resonance imaging (MR1), or magnetic resonance spectroscopic imaging (MRSI). Preferably, the compounds of the present invention comprise at least one carboxylic group, amide group, nitrogen, or oxygen group (preferably one or more of these groups, such as two, three, four or more) such that the specific metal of interest is effectively coordinated.

According to the present invention, said compound with at least one metal-sensitive chemical shift exhibits at least one NMR resonance with a metal-sensitive chemical shift in an NMR spectrum.

Preferably, the nucleus/nuclei (of the compounds of the present invention) which exhibits/exhibit a metal-specific chemical shift are hyperpolarizable.

According to the present invention, the compound is preferably based on several classes of metal chelators and is more preferably selected from the group of:

(IUPAC) name

pyro-EGTA 2,2',2",2'"-(2,2'-(l ,2-phenylene bis(oxy))bis(ethane-2, 1 -diyl))

bis(azanetriyl)tetraacetic acid

EGTA ethylene glycol-bis(2-aminoethylether)-N,N,N',N'-tetraacetic

acid

EDTA 2,2',2",2"'-(ethane-l ,2-diyldinitrilo)tetraacetic acid

(ethylenediamine tetraacetic acid)

AATA 2,2'-(2-(2-(2-(bis(carboxymethyl)amino)ethoxy)ethoxy)

phenylazanediyl)diacetic acid

APTRA 2-carboxymethoxy-aniline-N,N-diacetic acid

BAPTA 1 ,2-bis(-2-aminophenoxy)ethane- Ν,Ν,Ν',Ν'- tetraacetic acid

HIDA N-(2-hydroxyethyl)iminodiacetic acid

Carboxyglutamate 3 - Aminopropane- 1 , 1 ,3 -tricarboxylic acid

(CGlu)

citrate

arylazo chromotopic acid derivatives,

beta-diketone (crown-ether) derivatives,

mono-, di-, or tri-pyridyl aniline derivatives, mono-, di-, or tri-pyridyl amine derivatives,

trimethylphenylammonium derivatives and their hydrates, salts, solutions, stereoisomers, i.e. the hydrates, salts, solutions, stereoisomers of these compounds and derivatives.

A preferred compound with at least one metal-sensitive chemical shift is preferably selected from: pyro-EGTA, EGTA, EDTA, AATA, BAPTA, HIDA, citrate or a derivative or analog thereof, arylazo chromotopic acid derivatives, beta-diketone (crown-ether) derivatives, mono-, di-, or tri-pyridyl aniline derivatives, mono-, di-, or tri-pyridyl amine derivatives, trimethylphenylammonium derivatives ;

more preferably from: pyro-EGTA, EGTA, EDTA, AATA, BAPTA, HIDA, citrate or a derivative or analog thereof;

even more preferably from: pyro-EGTA, EGTA, EDTA or BAPTA, or a derivative or analog thereof.

In particular, the present invention provides the use of a compound with at least one metal- sensitive chemical shift for determining metal concentrations and/or measuring metal concentration changes,

by quantifying the NMR signal corresponding to said metal- specific chemical shift, preferably its intensity, frequency and/or bandwidth,

wherein the compound is selected from the group of:

pyro-EGTA,

EGTA,

EDTA,

AATA,

APTRA,

BAPTA,

HIDA,

citrate,

carboxyglutamate (CGlu),

or derivatives thereof; arylazo chromotopic acid derivatives, beta-diketone (crown-ether) derivatives,

mono-, di-, or tri-pyridyl aniline derivatives,

mono-, di-, or tri-pyridyl amine derivatives,

trimethylphenyl ammonium derivatives, and the hydrates, salts, solutions, stereoisomers of these compounds and derivatives.

Preferably, the compounds for determining metal concentrations and/or measuring metal concentration changes are selected from pyro-EGTA, EGTA, EDTA, AATA, BAPTA, HIDA, citrate or a derivative or analog thereof;

more preferably from: pyro-EGTA, EGTA, EDTA or BAPTA, or a derivative or analog thereof,

even more preferably from pyro-EGTA, EGTA and EDTA,

such as ^l3 C-EGTA, ¹³ C-pyro-EGTA and ¹³ C-EDTA

e.g.:

¹³ C-EDTA [2-[(2-{bis[carboxy( ¹³ C)methyl]amino}ethyl)[carboxy( ¹³ C)methyl]amino](l- ¹³ C) acetic acid],

¹³ C-EGTA [(3,12-bis[carboxy( ^l3 C)methyl](l ,14- ¹³ C ₂ )-6,9-di.oxa-3,12-diazatetradecanedioic acid],

or the perdeuterated variant ¹³ C-EGTA-d8 [(1,14-diethyl 3,12-bis[2-ethoxy-2- oxo( ² H2)ethyl](2,2, 13, 13- ² H4)-6,9-dioxa-3, 12-diazatetradecanedioate( ¹³ C ₄ )],

13

C-pyro-EGTA [2-({2-[2-(2-{bis[carboxy( ¹³ C)methyl]amino}ethoxy)-5-bromophenoxy] ethyl} [carboxy( ¹³ C)methyl]amino)(l- ¹³ C)acetic acid.

In particular, the present invention provides the use of a compound with at least one metal- sensitive chemical shift for detecting metal(s) qualitatively,

by quantifying the NMR signal corresponding to said metal-specific chemical shift, preferably its intensity, frequency and/or bandwidth,

wherein the compound is selected from the group of:

pyro-EGTA,

EGTA,

EDTA,

AATA, APTRA,

BAPTA,

HIDA,

citrate,

carboxyglutamate (CGlu),

or derivatives thereof; arylazo chromotopic acid derivatives,

beta-diketone (crown-ether) derivatives,

mono-, di-, or tri-pyridyl aniline derivatives,

mono-, di-, or tri-pyridyl amine derivatives,

trimethylphenylammonium derivatives, and the hydrates, salts, solutions, stereoisomers of these compounds and derivatives.

According to the invention, a "derivative" or "analog" of pyro-EGTA, EGTA, EDTA, AATA, APTRA, BAPTA, HIDA, citrate, carboxyglutamate (CGlu), arylazo chromotopic acid, beta- diketone (crown-ether), mono-, di-, or tri-pyridyl aniline, mono-, di-, or tri-pyridyl amine, trimethylphenylammonium is preferably selected from

- acids, amides, esters, ethers, pyridine, ketone,

- fluorinated analogs,

including perdeuterated analogs, ¹⁸ F radioisotopes, and their hydrates, salts, solutions, stereoisomers.

Perdeuterations or perdeuterated analogs are preferably to increase T _\ times.

For examples, see Figure 5, wherein such possible perdeuterations to increase Ti times are indicated by the symbol X.

Further preferred derivatives are compounds comprising at least one carboxylate, amide, nitrogen, oxygen group involved in coordinating of metals, such as shown as Ri in Figures 5A-I, that may in addition have variable residues as indicated as R _2> R ₃ and Y in Figures 5 A-I . For metal coordination, at least one carboxylate, amide, nitrogen or oxygen is required. A chemical shift can preferably be obtained either via a ^lj C, ^l3 N or ^,7 0 as part of the metal- coordination site or via electron transfer to 1H, ¹³ C , ¹⁵ N, ²⁹ Si, ³¹ P, ^l9 F, ⁸⁹ Yi residing e.g. on the meta or para position in pyro-EGTA, AATA, APTRA or BAPTA.

In one embodiment, the compound according to the present invention comprises further component (s).

Preferably, the further component(s) is/are selected from:

- label(s)

such as fluorophore(s), chi mophore(s), NIR dye(s),

e.g. cyanines for example indocyanine green (ICG) and derivatives, Bodipy and derivatives, squarine and derivatives, IR780 and derivatives and fluorescent proteins and chromoproteins,

radioisotope(s);

- photo- and/or thermolabile moiety/moieties

such as 6-nitroveratroyloxycarbonyl group (NVOC)

(see e.g. Ellies-Davies, 2008);

- macrocycle

preferably to stably hold a metal

such as to generate a stable chelate of Y and lanthanides;

- nanostructure(s),

including magnetic nanoparticles and ultrasound contrast agents, and/or

- radiocontrast agent(s).

The further component(s) is/are preferably covalently attached via functional or anchoring group(s).

For example, the compounds / metal-specific sensors of the present invention can be modified such that bioconjugation/attachment of further component(s) can be easily achieved via suitable functional or anchoring group(s).

Figures 5 A-I shows examples of possible modifications. Such as:

(i) via amine chemistry, preferably with photolabile moieties/groups

such as 6-nitroveratroyloxycarbonyl group (NVOC)

The photolabile moieties/groups can be connected to an a-carbon of the amine groups to get photolabile metal sensors. After photocleavage, the metal will be released non-reversibly. This is e.g. of interest to prevent contribution of non-signal generating compounds (e.g. after a time interval much longer than the relaxation time has passed) to the metal chelation capacity, e.g. if repeated measurements with hyperpolarized compounds are to be performed.

(ii) Furthermore, fluorophores , chromophores, radioisotopes can be connected to the chelators/ compounds / metal-specific sensors of the present invention

e.g. via C-C, C-N or C-O,

to e.g. validate their localization (measure their concentration for ratiometric approaches) by fluorescent microscopy. If the fluorophore is attached close to an aromatic ring, e.g. via C-C, C-N or C-O, chemical-shift inducing metal binding can also lead to simultaneous changes in fluorescence allowing for bimodal detection via MRI and fluorescence.

- Metal-sensitivity

Preferably, the compound according to the present invention is labeled with ^! H, ¹³ C, ¹⁵ N, ¹⁹ F, Si, P, Y or combinations thereof.

More preferably, the compound exhibits at least one metal-sensitive chemical shift of the ¹ H, ¹³ C, ¹⁵ N, ¹⁹ F, ²⁹ Si, ³¹ P and/or ⁸⁹ Y nuclei.

More preferably, the compound according to the present invention exhibits a chemical shift that is specific for the particular metal, such that in one embodiment more than one metal (such as two, three, four or more) can be detected in parallel / at the same time.

Preferably, the compound exhibits at least one metal-sensitive chemical shift sensitive physiological and/or pathological metal concentration range.

A "physiological pH" or "physiological pH range" refers to pH ranges from about 5 to about 9, preferably a "physiological pH" or "physiological pH range" is from about pH 6 to about 8. In a preferred embodiment, the compound is hyperpolarized.

Hyperpolarization of NMR active ¹³ C, ¹⁵ N nuclei may be achieved by different methods, which are for instance described in WO 98/30918, WO 99/24080 and WO 99/35508, and hyperpolarization methods are polarization transfer from a noble gas, "brute force", spin refrigeration, the parahydrogen method (ParaHydrogen Induced Polarisation (PHIP)) and Dynamic Nuclear Polarization (DNP).

Preferably, the hyperpolarization is done by Dynamic Nuclear Polarization (DNP).

The term "hyperpolarized" refers to a nuclear polarization level in excess of 0.1%, more preferred in excess of 1% and most preferred in excess of 10%. The level of polarization may for instance be determined by solid state NMR measurements, such as in solid hyperpolarized pyro-EGTA, EGTA, EDTA, AATA, APTRA, BAPTA, HIDA, citrate, carboxyglutamate (CGlu), arylazo chromotopic acid, beta-diketone (crown-ether), mono-, di-, or tri-pyridyl aniline, mono-, di-, or tri-pyridyl amine, trimethylphenylammonium (or other compounds, such as derivatives or analogs thereof), e.g. obtained by dynamic nuclear polarization (DNP) of pyro-EGTA, EGTA, EDTA, AATA, APTRA, BAPTA, HIDA, citrate, carboxyglutamate (CGlu), arylazo chromotopic acid, beta-diketone (crown-ether), mono-, di-, or tri-pyridyl aniline, mono-, di-, or tri-pyridyl amine, trimethylphenylammonium (or other compounds, such as derivatives or analogs thereof).

The solid state NMR measurement preferably consists of a simple pulse-acquire NMR sequence using a low flip angle. The signal intensity of the hyperpolarized nucleus in the NMR spectrum is compared with signal intensity in a NMR spectrum acquired before the polarization process. The level of polarization is then calculated from the ratio of the signal intensities before and after polarization. In a similar way, the level of polarization for dissolved hyperpolarized pyro-EGTA, EGTA, EDTA, AATA, APTRA, BAPTA, HIDA, citrate, carboxyglutamate (CGlu), arylazo chromotopic acid, beta-diketone (crown-ether), mono-, di-, or tri-pyridyl aniline, mono-, di-, or tri-pyridyl amine, trimethylphenylammonium (or other compounds, such as derivatives or analogs thereof) may be determined by liquid state NMR measurements. Again the signal intensity of the dissolved hyperpolarized pyro- EGTA, EGTA, EDTA, AATA, APTRA, BAPTA, HIDA, citrate, carboxyglutamate (CGlu), arylazo chromotopic acid, beta-diketone (crown-ether), mono-, di-, or tri-pyridyl aniline, mono-, di-, or tri-pyridyl amine, trimethylphenylammonium (or other compounds, such as derivatives or analogs thereof) is compared with the signal intensity before polarization. The level of polarization is then calculated from the ratio of the signal intensities before and after polarization.

In one embodiment, the 1H, ¹³ C, ¹⁵ N, ¹⁹ F, ²⁹ Si, ³¹ P and/or ⁸⁹ Y nuclei belonging to the metal- sensitive and metal-specific chemical shift(s) of the compound of the present invention exhibit(s) a long longitudinal relaxation time Ίχ and/or an optimized dynamic range of the metal concentration of interest.

The term "long longitudinal relaxation time Ti" as used herein refers to a relaxation time of several seconds.

The term "an optimized dynamic range" for the metal concentration of interest as used herein refers to the dissociation constants of the compound-metal complex to be matched such that the steep portion of the binding curve covers the relevant range for the metal concentrations to be determined, i.e. a small change in the metal concentration is detected by a large change in the signal obtained from the compound.

- Chemical shift reference

Preferably, a reference chemical shift which is metal-insensitive, i. e. not metal-sensitive and, thus, exhibits no change in chemical shift upon change of metal concentration, is required. This is typically provided in the form of a further compound, the "reference compound", that is added to or also present in a sample.

Alternatively, a chemical shift with a different correlation between the metal concentration and the chemical can serve as a reference. This may, e.g., be a chemical shift within the compound according to the present invention.

The reference chemical shift can be an endogenous reference or an exogenous reference or a chemical shift of the compound itself or its metabolites. In one embodiment, the compound with one or more metal-sensitive chemical shifts of the invention furthermore exhibits at least one chemical shift that is not metal-sensitive, preferably at least one metal-insensitive ^! H and/or C and/or ^I5 N and/or ¹⁹ F and/or ²⁹ Si and/or ³¹ P and/or ⁸⁹ Y chemical shift (endogenous reference).

In one embodiment, a reference compound is used. The reference compound is a compound which does not exhibit metal-sensitive shift(s) (exogenous reference).

Preferably the reference compound is labeled with Ή and/or ¹³ C and/or ¹⁵ N and/or ¹⁹ F and/or ²⁹ Si and/or ³¹ P and/or ⁸⁹ Y-labelled and preferably exhibits at least one metal-insensitive chemical shift.

A preferred reference compound (for ¹³ C) is ^lj C methanol or ¹³ C urea.

As discussed above, the present invention provides an imaging medium, comprising at least one compound with at least one metal-sensitive chemical shift as defined herein, optionally, pharmaceutically acceptable earners and/or excipients, such as an aqueous carrier, like a buffer.

Preferably, the imaging medium is a magnetic resonance (MR) imaging medium.

The term "imaging medium" refers to a liquid composition comprising at least one compound with one or more metal-sensitive chemical shifts of the present invention (such as hyperpolarized compounds as listed in Figure 5, including pyro-EGTA, EGTA, EDTA, AATA, APTRA, BAPTA, HIDA, citrate, carboxyglutamate (CGlu), arylazo chi motopic acid, beta-diketone (crown-ether), mono-, di-, or tri-pyridyl aniline, mono-, di-, or tri-pyridyl amine, trimethylphenylammonium (or other compounds, such as derivatives or analogs thereof) as the MR active agent. The imaging medium according to the invention may be used as imaging medium in MR imaging or as MR spectroscopy agent in MR spectroscopy. The imaging medium according to the invention may be used as imaging medium for in vivo MR imaging and/or spectroscopy, i.e. MR imaging and/or spectroscopy carried out on living human or non-human animal beings. Further, the imaging medium according to the invention may be used as imaging medium for in vitro MR imaging and/or spectroscopy, e.g. for determining metal concentration and/or metal concentration changes in cell cultures or ex vivo tissues. Cell cultures may be derived from cells obtained from samples derived from the human or non-human animal body, like for instance blood, urine, stool, semen, saliva or mucous fluids, while ex vivo tissue may be obtained from biopsies or surgical procedures.

In one embodiment, the imaging medium preferably comprises in addition to the MR active agent an aqueous carrier, preferably a physiologically tolerable and pharmaceutically accepted aqueous carrier, like water, a buffer solution or saline. Such an imaging medium may further comprise conventional pharmaceutical or veterinary carriers or excipients, e.g. formulation aids such as are conventional for diagnostic compositions in human or veterinary medicine.

In one embodiment, the imaging medium preferably comprises in addition to the MR active agent a solvent which is compatible with and used for in vitro cell or tissue assays, for instance DMSO or methanol or solvent mixtures comprising an aqueous carrier and a nonaqueous solvent, for instance mixtures of DMSO and water or a buffer solution or methanol and water or a buffer solution.

Preferably, at least one compound with at least one or more metal-sensitive chemical shifts is used in concentrations of up to 1 M, preferably 0.1 to 100 mM, such as 10 to 80 mM, in the imaging medium.

As discussed above, the present invention provides a biosensor for determining metal concentrations and/or measuring metal concentration changes.

Said biosensor comprises:

(i) at least one compound with at least one metal-sensitive chemical shift according to the present invention,

(ii) one or several further components selected from pharmaceutically acceptable carriers, moieties interacting with biological targets and/or pharmaceutically acceptable excipients,

(iii) optionally, a reference compound.

The one or several further components are selected from pharmaceutically acceptable carriers, moieties interacting with biological targets and/or pharmaceutically acceptable excipients. A moiety or moieties interacting with biological target(s), in particular to alter the biodistribution and pharmacokinetics of the compounds/biosensor of the present invention, can be

- biomolecules,

such as

antibodies, nanobodies, proteins or DNA/RNA aptamers with affinity for proteins, or DNA or RNA, lipids, sugars,

- encapsulation into micelles, protein/DNA capsids/shells,

- conjugation onto multidentate scaffolds

such as

polymers, dendrimers, or

- conjugation onto surfaces of nanostructures.

Suitable pharmaceutically acceptable carriers and/or excipients are known in the art. Said biosensor can optionally further comprise

(iv) label(s) (such as fluorophore(s), chromophore(s), NIR dye(s), radioisotope(s))

photo- and/or thermolabile moiety/moieties

macrocycle

nanostructure(s),

and/or

radiocontrast agent(s)

as described above.

In one embodiment, the reference compound is a compound which does not exhibit metal- sensitive chemical shift(s) in an NMR spectrum (exogenous reference chemical shift, as described above).

Preferably, the reference compound is ^] H and/or ¹³ C and/or ¹⁵ N and/or ¹⁹ F and/or ²⁹ Si and/or ³ P and/or ⁸⁹ Y-labelled,

and preferably exhibits at least one metal-insensitive 1H and/or ¹³ C and/or ¹⁵ N and/or ¹⁹ F and/or ²⁹ Si and/or ^{3 I} P and/or ⁸⁹ Y chemical shift. Alternatively, a chemical shift with a different correlation between metal concentration and chemical shift can serve as a reference.

13 13

A preferred reference compound is C-urea or C-methanol.

For example, the reference compound is obtained in that a substance or compound (such as urea) is co-polarized at the same time when the compound with one or more metal-sensitive chemical shifts of the invention is hyperpolarized.

Preferably, the at least one compound with at least one/one or more metal-sensitive chemical shift is used in concentrations of up to 1 M, preferably 0.1 to 100 mM, such as 10 to 80 mM, in the biosensor.

- Samples

The compounds of the present invention and/or the biosensor of the present invention are suitable to be used in samples, such as

- biological fluids,

such as blood, urine, lymph, cerebrospinal fluid, stool, semen, saliva or mucous fluids,

- cell culture samples

such as derived from the human or non-human animal body, ex vivo tissue, cell culture.

Also cell cultures may be derived from cells obtained from samples derived from the human or non-human animal body (like for instance blood, urine, lymph, cerebrospinal fluid, stool, semen, saliva or mucous fluids), while ex vivo tissue may be obtained from biopsies or surgical procedures.

Imaging and medical uses

As discussed above, the present invention provides the compound with at least one metal- sensitive chemical shift of the present invention (the imaging medium of the present invention) or the biosensor of the present invention for use in in vivo magnetic resonance imaging (MRJ), magnetic resonance spectroscopy (MRS) or magnetic resonance tomography (MRT). As discussed above, the present invention provides the compound with at least one metal- sensitive chemical shift of the present invention or the biosensor of the present invention for use in absorbance/transmission, reflection, fluorescence or o toacoustic or ultrasound measurements and imaging.

In particular, the present invention provides the compound with at least one metal-sensitive chemical shift of the present invention (the imaging medium of the present invention) or the biosensor of the present invention for use in in vivo magnetic resonance imaging (MRI), or magnetic resonance spectroscopy (MRS) with optional multimodal detection of additional label(s), preferably as defined herein, via absorbance/transmission, reflection, fluorescence or optoacoustic or ultrasound measurements and imaging.

As used herein "multimodal detection" refers to the combined detection of the compound of the present invention or the biosensor of the present invention via a detection method that is not be based on the NMR, such as PET, ultrasound or photon-dependent methods.

In one embodiment, the magnetic resonance readout can be combined with photon-dependent imaging via transmission, fluorescence, or optoacoustic imaging techniques detecting a chromophore inserted.

As used herein "optoacoustic or photoacoustic" measurements or imaging refer to the detection of the mechanical waves generated by the optoacoustic, or photoacoustic effect (Ntziachristos et a!., 2010)

As used herein "fluorescent or absorption" measurements or imaging refer to the detection of fluorescent and/or absorbed photons for point measurements or spatiotemporally resolved measurements/imaging.

As discussed above, the present invention provides the compound with at least one metal- sensitive chemical shift of the present invention or the biosensor of the present invention for use in diagnosing and/or monitoring treatment of diseases causing changes in metal concentrations.

Thereby, the progress of a disease and/or the treatment of a disease can be monitored. In one embodiment, the use is for in vivo diagnosing and/or monitoring treatment of diseases causing changes in metal concentrations.

Preferably, a "disease causing changes in metal concentrations" is selected from:

(1) diseases in which calcium signaling is affected

as in:

neuropsychiatric diseases, such as epilepsy,

stroke,

brain damage,

neurodegenerative diseases,

states of altered neuronal processing, such as sleep, coma, anesthesia, intoxication,

cardiovascular diseases, such as arrhythmias, cardiac ischemia and myocardial infarct,

neuromuscular or muscular diseases,

(2) diseases in which calcium and/or magnesium uptake, storage, utilization or excretion is affected

as in

endocrinological conditions, such as hyper/hypoparathyroidism, malnutrition and gastrointestinal diseases, such as malabsorption and diarrhea e.g. due to alcoholism,

bone-related diseases, such as osteoporosis,

kidney diseases and treatment with diuretics.

osteoclastic processes of tumors or infections,

diseases in which calcification in tissues occurs, such as cancers, including breast cancer,

atherosclerotic alterations or inflammatory processes,

due to other medical treatments,

(3) diseases in which iron uptake, storage, utilization or excretion is affected

as in

iron-deficit caused by e.g. malnutrition or blood loss, or anemia including genetically-caused anemias, infections and inflammation, neurodegenerative diseases, medical treatments (4) diseases in which uptake, storage, utilization or excretion of other metals is affected as in

neurodegenerative diseases {e.g. zinc, copper), or metal storage diseases, such as Wilson's disease, tumors, such as melanomas,

medical treatments,

(5) diseases caused by metal intoxications

with e.g. arsenic, cadmium, lead, manganese, nickel, cobalt, mercury.

Preferably, the imaging is real-time.

Preferably, the uses comprise the resolution of the spatiotemporal metal distribution,

(such as spatiotemporal resolution to repeatedly capture spatiotemporal metal distributions), preferably, comprising the use of frequency encoding techniques, such as all methods of chemical shift imaging (CSI) and phase sensitive encodings of chemical shifts (as e.g. used in non-invasive spatially resolved temperature measurements using changes in proton resonance frequencies (0.01 ppm/°C)). See Rieke et al , 2004.

Preferably, the use comprises monitoring extra- and intracellular calcium signaling and (treatments of) metal metabolism and intoxication in preclinical animal models, such as zebrafish, rodents and non-human primates.

In one embodiment, multimodal imaging via absorbance, fluorescence or optoacoustics, is used in addition, and/or the metal coordination and pharmacokinetics of the biosensor are controlled via breaking the photolabile and/or thermolabile moieties, if present and as specified herein above.

As discussed above, the present invention provides the compound with at least one metal- sensitive chemical shift of the present invention or the biosensor of the present invention as metal sensor for in vitro or ex-vivo NMR spectroscopy.

The metal sensor is suitable for in vitro or ex-vivo NMR spectroscopy in non-biological and biological samples, preferably in samples containing biological cells. As discussed above samples can be

- biological fluids,

such as blood, urine, lymph, cerebrospinal fluid, stool, semen, saliva or mucous fluids,

- cell culture samples

such as derived from the human or non-human animal body, ex vivo tissue, cell culture.

Also cell cultures may be derived from cells obtained from samples derived from the human or non-human animal body (like for instance blood, urine, lymph, cerebrospinal fluid, stool, semen, saliva or mucous fluids), while ex vivo tissue may be obtained from biopsies or surgical procedures.

Preferably, the use comprises response-to-treatment monitoring of treatments applied to cell lines, tissue cultures or explanted tissue.

Preferably, the use comprises monitoring extra- and intracellular calcium signaling and (treatments of) metal metabolism and toxicity in tissue culture and cell lines.

Methods for determining metal concentration and/or measuring metal concentration changes As discussed above, the present invention provides an in vitro as well as an in vivo method for determining metal concentration and/or measuring metal concentration changes.

Said in vitro method comprises the steps of

(i) providing a sample,

(ii) adding a compound with at least one metal-sensitive chemical shift of the present invention or a biosensor of the present invention to the sample,

(iii) performing magnetic resonance imaging (MRI), nuclear magnetic resonance (NMR) spectroscopy or magnetic resonance spectroscopy imaging (MRS I) and thereby determining the spatial distribution of metal concentration or metal concentration changes of or in the sample

(1) by obtaining a chemical shift difference between at least one metal- sensitive chemical shift of the compound and a metal-independent chemical shift, such metal- independent chemical shift acting as a reference chemical shift, or

(2) by measurement of the absolute chemical shift, or (3) by measuring chemical shift differences involving at least one metal-sensitive shift,

optionally, by obtaining additional measurements of metal-insensi tive signals that relate to the concentration of said compound or biosensor of the present invention, for instance based on radioactivity, absorbance, fluorescence, optoacoustic or ultrasound signal from said compound or biosensor of the present invention containing the appropriate radioactive moiety, fluorophore/chromophore, preferably measuring simultaneously the spatiotemporal distribution of several metals at once based on the metal-specific chemical shifts, e.g. the Mg ²⁺ , Ca ²⁺ and Zn ²⁺ simultaneously with parallel determination of pH.

Preferably, the compound or biosensor has been hyperpolarized and/or resolved, before it is added to the sample in step (ii).

Preferably, the sample is a cell culture sample, such as derived from a human or non-human body, ex vivo tissue, cell culture.

Preferably, step (iii) is carried out in an MRI scanner machine with MRS or MRSI capabilities or in a NMR spectrometer (such as via a micro imaging head).

In one embodiment, the metal-independent chemical shift (acting as a reference chemical shift) is from the same compound, i.e. the compound with at least one metal- sensitive chemical shift (endogenous reference chemical shift, as described above), or from another substance (exogenous reference chemical shift, as described above), and is used as a metal- independent reference.

Alternatively, a chemical shift with a different correlation between metal concentration and chemical shift can serve as a reference.

In one embodiment, said in vitro method comprises the steps of

(i) providing a sample,

(ii) adding a compound with at least one metal-sensitive chemical shift of the present invention or a biosensor of the present invention to the sample, wherein the compound or biosensor has been hyperpolarized and/or resolved,

(iii) performing magnetic resonance imaging (MRI), nuclear magnetic resonance (NMR) spectroscopy or magnetic resonance spectroscopy imaging (MRSI) and thereby detennining the spatial distribution of metal concentration or metal concentration changes of or in the sample

by obtaining the chemical shift and/or the integrated peak area and/or peak amplitude of the signal at that chemical shift from at least one metal- sensitive chemical shift and by relating these values via a modeled or measured reference binding curve to the metal concentration, whereby

spatiotemporally resolved metal-sensitive signals can be corrected for differences in local and time-dependent signal intensities, e.g. due to differences in the local concentration of the metal sensor(s) (i.e. the compound or biosensor of the present invention),

by measurements of the absolute chemical shift, integrated peak area or peak amplitude,

or

by obtaining the chemical shift and/or the integrated peak area and/or peak amplitude of the signal at that chemical shift from at least one metal- sensitive chemical shift and a reference signal in the form of a chemical shift and/or integrated peak area from at least one metal-sensitive or metal- insensitive chemical shift, or a function of several chemical shifts, such as their ratio or sum,

wherein the reference signal may be measured from a metal-sensitive or metal-insensitive MRI signal from another nucleus such as 1H, ^lj C, ⁱ⁵ N, ¹⁹ F, 2 ⁹ Si, ³¹ P and/or ⁸⁹ Y,

or wherein the reference signal may be measured via e.g. another method such as Positron Emission Tomography (PET) or fluorescence or optoacoustics or ultrasound

(iv) calculating metal concentration maps based on spatially resolved metal concentration values or metal concentration changes determined in step (iii), wherein step (iii) preferably comprises comparing said relative chemical shifts to predetermined or simultaneously measured calibration curves of the compound with at least one metal- sensitive chemical shift in solutions with known metal concentration or mixtures of metals with known concentrations, wherein the sample is preferably a cell culture sample such as derived from a human or non- human body, ex vivo tissue, cell culture

As discussed above samples can be

- biological fluids,

such as blood, urine, lymph, cerebrospinal fluid, stool, semen, saliva or mucous fluids;

- cell culture samples

such as derived from the human or non-human animal body, ex vivo tissue, cell culture.

Also cell cultures may be derived from cells obtained from samples derived from the human or non-human animal body (like for instance blood, urine, lymph, cerebrospinal fluid, stool, semen, saliva or mucous fluids), while ex vivo tissue may be obtained from biopsies or surgical procedures.

As discussed above, the present invention provides an in vitro as well as an in vivo method for determining metal concentration and/or measuring metal concentration changes.

Said in vivo method of the present invention comprises the steps of

(i) applying or administering a compound with at least one metal-sensitive chemical shift of the present invention or a biosensor of the present invention to the body of a patient or non- human animal,

(ii) performing magnetic resonance imaging (MRI) and thereby determining one or several metal concentrations or metal concentration changes of or in the body of said patient or non-human animal

(1) by correcting a spatiotemporally resolved metal- sensitive signal for differences in local and time-dependent signal intensities, e.g. due to differences in the local concentration of the metal sensors, and

by obtaining the chemical shift and/or its integrated peak area and/or peak amplitude from at least one metal-sensitive chemical shift and a metal-insensitive reference in the form chemical shift and/or integrated peak area from at least one metal-insensitive chemical shift or a function of metal- sensitive shifts,

or

(2) by measurement of the absolute chemical shift, integrated peak area or peak amplitude,

wherein the reference signal is obtained

by measuring a metal-insensitive MRI signal from another nucleus such as proton via a lanthanide, 1H, ¹³ C, ¹⁵ N, ¹⁹ F, ²⁹ Si, ³¹ P and/or ⁸⁹ Y, or

by combination with another method, such as a PET measurement, or fluorescence or optoacoustics or ultrasound.

Preferably, the in vivo method is a real-time method.

In one embodiment, the patient is human.

Preferably, the compound or biosensor has been hyperpolarized and/or resolved, before it is administered or applied in step (i).

Preferably, the patient can be diagnosed with a disease causing changes in metal concentrations or the treatment of a disease causing changes in metal concentrations can be monitored.

Preferably, a "disease causing changes in metal concentrations" is preferably selected from the diseases as defined above.

In one embodiment, said in vivo method comprises the steps of

(i) applying or administering a compound with at least one metal-sensitive chemical shift of the present invention or a biosensor of the present invention to the body of a patient or non- human animal,

wherein the compound or biosensor has been hyperpolarized and/or resolved,

(ii) perforoiing magnetic resonance imaging (MRI) and thereby determining one or several metal concentrations or metal concentration changes of or in the body of said patient or non-human animal

by obtaining the chemical shift and/or the integrated peak area and/or peak amplitude of the signal at that chemical shift from at least one metal- sensitive chemical shift and by relating these values via a modeled or measured reference binding curve to the metal concentration, whereby

spatiotemporally resolved metal-sensitive signals can be corrected for differences in local and time-dependent signal intensities, e.g. due to differences in the local concentration of the metal sensors

by measurements of the absolute chemical shift, integrated peak area or peak amplitude,

or

by obtaining the chemical shift and/or the integrated peak area and/or peak amplitude of the signal at that chemical shift from at least one metal- sensitive chemical shift and a reference signal in the form of a chemical shift and/or integrated peak area from at least one metal- sensitive or metal- insensitive chemical shift, or a function of several chemical shifts such as their ratio or sum

wherein the reference signal may be measured from a metal- sensitive or metal-insensitive MRI signal from another nucleus such as ^J H, ¹³ C, ¹⁵ N, ¹⁹ F, 2 ⁹ Si, ^3, P and/or ⁸⁹ Y,

or wherein the reference signal may be measured via e.g. another method such as Positron Emission Tomography (PET) or fluorescence or optoacoustics or ultrasound

(iii) calculating metal concentration maps based on spatially resolved metal concentration values or metal concentration changes determined in step (ii), wherein step (ii) preferably comprises comparing said relative chemical shifts to predetermined or simultaneously measured calibration curves of the compound with at least one metal- sensitive chemical shift in solutions with known metal concentration or mixtures of metals with known concentrations.

wherein the patient can preferably be diagnosed with a disease causing changes in metal concentrations or the treatment of a disease causing changes in metal concentrations can be monitored. In one embodiment, the metal-independent chemical shift (acting as a reference chemical shift) is from the same compound, i.e. the compound with at least one metal-sensitive chemical shift (endogenous reference chemical shift, as described above), or from another substance (exogenous reference chemical shift, as described above), and is used as a metal- independent reference.

Alternatively, a chemical shift with a different correlation between metal concentration and chemical shift can serve as a reference.

Preferably, the in vitro and/or the in vivo method comprises the resolution of the spatial metal distribution and, thus, obtaining spatially resolved NMR spectra,

preferably, comprising the use of frequency encoding techniques, such as all methods of chemical shift imaging (CSI) and phase sensitive encodings of chemical shifts (as e.g. used in non-invasive spatially resolved temperature measurements using changes in proton resonance frequencies (0.01 ppm/0 C) (see Rieke et ah , 2004),

as well as indirect methods based on detecting protons in proximity of the other nucleus, such as C or N proton-observed carbon-edited (POCE) sequences and its analogs, as well as CEST or Magnetization Transfer (MT) methods.

Methods for diagnosing and/or monitoring treatment

As discussed above, the present invention provides a method of diagnosing and/or monitoring treatment of a disease causing changes in metal concentrations.

Said method comprises the steps of

(i) applying or administering a compound with at least one metal-sensitive chemical shift of the present invention or a biosensor of the present invention to the body of a patient or non- human animal,

(ii) performing magnetic resonance imaging (MRJ) or magnetic resonance spectroscopy (MRS) and thereby determining one or several metal concentrations or metal concentration changes of or in the body of said patient or non-human animal

(1) by obtaining over time the chemical shift and/or its integrated peak area and/or its peak amplitude from at least one metal- sensitive chemical shift and a metal- insensitive reference in the form of a chemical shift and/or its integrated peak area and/or peak amplitude from at least one metal-insensitive chemical shift or a function of metal-sensitive shifts,

or

(2) by measurement of the absolute chemical shift, integrated peak area or peak amplitude,

wherein the reference signal is obtained

by measuring a metal -insensitive MRI signal from another nucleus such as proton via a lanthanide, Ή, ¹³ C, ¹ N, ¹⁹ F, ²⁹ Si, ³¹ P and/or ⁸⁹ Y, or

by combination with another method, such as a PET measurement, or fluorescence or optoacoustics or ultrasound,

(iii) calculating metal concentration maps based on spatially resolved metal concentration values or metal concentration changes determined in step (ii),

Preferably, the compound or biosensor has been hyperpolarized and/or resolved, before it is administered or applied in step (i).

Preferably, a "disease causing changes in metal concentrations" is preferably selected from the diseases as defined herein above.

Thereby, the progress of a disease and/or the treatment of a disease can be monitored.

Preferably, step (iii) preferably comprises

comparing said relative chemical shifts to predetermined or simultaneously measured calibration curves of the compound with at least one metal-sensitive chemical shift in solutions with known metal concentration or mixtures of metals with known concentrations.

In one embodiment, said method furthermore comprises

hyperpolarizing the compound with at least one metal-sensitive chemical shift before application or administration to the body of the patient.

Thereby, the compound is hyperpolarized by any hyperpolarization methods, such as dissolution Dynamic Nuclear Polarization (DNP) or ParaHydrogen Induced Polarisation (PHIP). Preferably, the method comprises magnetic resonance tomography (MRT). Preferably, the imaging is real-time.

Preferably, the method comprises the resolution of the spatial metal distribution and, thus, obtaining spatially resolved NMR spectra, preferably, comprising the use of frequency encoding techniques, such as all methods of chemical shift imaging (CSI) and phase sensitive encodings of chemical shifts (as e.g. used in non-invasive spatially resolved temperature measurements using changes in proton resonance frequencies (0.01 ppm/0 C) (see Rieke et al, 2004),

as well as indirect methods based on detecting protons in proximity of the other nucleus, such

13 15

as C or N proton-observed carbon-edited (POCE) sequences and its analogs, as well as CEST or Magnetization Transfer (MT) methods.

Further uses

As discussed above, the present invention provides the use of a compound of the present invention or the biosensor of the present invention in quality control of food or in the examination of plants and organisms,

or for monitoring of environmental resources, including air, water, and soil with respect to pollution and harmful metal concentrations.

Derivatives of EDTA and EGTA

As discussed above, the present invention provides derivatives or analogs of EDTA and EGTA.

Said EDTA and EGTA derivatives comprise one or more hyperpolarizable nuclei,

e.g. ¹³ C, ¹⁹ F, or ³¹ P, ²⁹ Si, ¹⁵ N, or N¾

which is/are positioned close to the metal-coordinating moieties such that a metal-specific chemical shift can be obtained,

Preferred examples are: ¹³ C-EDTA [2^(2-{bis[carboxy( ⁱ³ C)methyl]amino}ethyl)[carboxy( ¹³ C)iiiethyl]amino](l- ¹³ C) acetic acid],

^,3 C-EGTA [(3,12-bis[carboxy( ^I3 C)methyl](l J 4- ¹³ C ₂ )-6,9-dioxa-3,12-diazatetradecanedioic acid],

or the perdeuterated variant ¹³ C-EGTA-d8 [(1,14-diethyl 3,12-bis[2-ethoxy-2- oxo( ² H ₂ )ethyl](2,2,13,13- ² H4)-6,9-dioxa-3, 12-diazatetradecanedioate( ¹³ C ₄ )].

As can be seen e.g. in Figure 7.

As discussed above, the present invention provides the derivatives or analogs EDTA and EGTA of the present invention for use as metal biosensors, i.e. the uses and in the methods according to the present invention, as discussed herein above.

Derivatives of pyro-EGTA, AATA, APTRA and B APT A

As discussed above, the present invention provides derivatives or analogs of pyro-EGTA, AATA, APTRA or BAPTA.

The derivatives or analogs of pyro-EGTA, AATA, APTRA or BAPTA of the present invention comprise a "modifying moiety" or "modifying moieties". Said modifying moiety/moieties or group(s) alter(s) the affinity for metals (and are thus referred to as "metal affinity modifying moiety" or "metal affinity modifying moieties").

Said modifying moiety/moieties is/are preferably selected from:

- halogen (e.g. CI, Br, I),

-a hyperpolarizable nucleus (e.g. ^I9 F, or ³¹ P, ²⁹ Si, ¹⁵ N), or

-N¾,

Suitable examples for said modifying moieties are shown in Figures 5B to 51, see Ri and R ₂ .

The derivatives are preferably compounds comprising at least one carboxylate, amide, nitrogen, oxygen group involved in coordinating of metals, such as shown as Ri in Figures 5A-1, that may in addition have variable residues as indicated as R _2j R ₃ and Y in Figures 5A-I . For metal coordination, at least one carboxylate, amide, nitrogen or oxygen is required. A chemical shift can preferably be obtained either via a ¹³ C, ¹⁵ N or ¹⁷ 0 as part of the metal- coordination site or via electron transfer to ^l R, ¹³ C , ¹⁵ N, ²⁹ Si, ³¹ P, ^!9 F, ⁸⁹ Yi residing e.g. on the meta or para position in pyro-EGTA, AATA, APTRA or BAPTA.

For example,

- As shown in Figure 5C, for pyro-EGTA, suitable metal affinity modifying moieties or groups are e.g.

¹³ COOH, ¹³ CONHCH ₃ , ¹³ COOCH ₂ OCOCH ₃ ,

Br, ¹⁹ F, or ³¹ P, ²⁹ Si, ¹⁵ N, ¹⁵ N (CD ₃ ) ₃ , NH ₂

- As shown in Figure 5D, for AATA, suitable modifying moieties or groups are e.g.

1 ³ COOH, ¹³ CONHCH ₃ , ¹³ COOCH ₂ OCOCH ₃ ,

Br, ¹⁹ F, or ³¹ P, ²⁹ Si, ¹⁵ N, ¹⁵ N (CD ₃ ) ₃ , NH ₂

- As shown in Figure 5E, for APTRA, suitable modifying moieties or groups are e.g.

1 ³ COOH, ¹³ CONHCH ₃ , ^,3 COOCH ₂ OCOCH ₃ ,

Br, ¹⁹ F, or ³¹ P, ²⁹ Si, ¹⁵ N, ¹⁵ N (CD ₃ ) ₃ , NH ₂

- As shown in Figure 5F, for BAPTA, suitable modifying moieties or groups are e.g.

1 ³ COOH, ¹³ CONHCH ₃ , ¹³ COOCH ₂ OCOCH ₃ ,

Br, ¹⁹ F, or ³¹ P, ²⁹ Si, ¹ N, ¹⁵ N (CD ₃ ) ₃ , NH ₂

Preferred embodiments of the derivatives or analogs are

¹³ C-pyro-EGTA [2-({2-[2-(2-{bis[carboxy( ¹³ C)methyl]amino}ethoxy)-5-bromophenoxy] ethyl} [carboxy( ¹³ C)methyl]amino)(l - ¹³ C)acetic acid,

Bromo-pyro-EGTA and ¹⁹ F-pyro-EGTA.

As discussed above, the present invention provides the derivatives or analogs of pyro-EGTA, AATA, APTRA or BAPTA of the present invention for use as metal biosensors, i.e. the uses and in the methods according to the present invention, as discussed herein above. Further description of preferred embodiments

The features of the metal biosensors of the present invention are: a) chemical shift

- metal-specific chemical shift

- that is robust against pH changes

- in the case of EDTA (and its derivatives), pH can be measured simultaneously with calcium

- tunable sensitivity and specificity for different metals

- compounds are hyperpolarizable to achieve stronger signals for in vivo applications b) coupling of further component(s) is possible, such as via functional group(s):

wherein such further components can be:

- biomolecule(s),

- photolabile moiety/moieties,

- label(s): chromophore(s), fluorophore(s), NIR dye(s), radioisotope(s)

The inventors show that the metal-specific chemical shift of the metal biosensor compounds of the present invention, in particular or EDTA and EGTA, is independent of the pH shifts. In the case of EDTA, pH can be read out simultaneously with the metal content.

The inventors furthermore show that calcium can be detected quantitatively in the presence of another metal, namely magnesium, by the metal biosensor compounds of the present invention (in particular EDTA and EGTA) based on the metal-specificity of the chemical shift, in particular of EDTA and EGTA, Moreover, the apparent affinity of calcium in the presence of magnesium is reduced as is desired for detection of extracellular magnesium levels.

As discussed above, Nonaka et al. (2013) have recently published a ^{I 5} N-containing compound, namely [ ¹⁵ N, D ₉ ]trimethylphenylanrmonium ([ ¹⁵ N, D ₉ ]TMPA) that can be hyperpolarized by DNP and exhibits a chemical shift of the ¹⁵ N moiety when coupled to a metal chelator APTRA.

In distinction to Nonaka et al. (2013), the hyperpolarizable compounds disclosed in the present document exhibit (1) a metal-specific, reversible chemical shift that e.g. allows for detection of calcium in the presence of equimolar concentrations of magnesium;

(2) robustness of metal- sensitive shift against pH changes with the ability to readout pH in parallel (e.g. as shown for C-EDTA),

(3) a wide range of tuned dissociation constants.

- Abstract

Specific sensing of metals in opaque and scattering biomedical or environmental samples in a non-invasive, photon-independent way by Nuclear Magnetic Resonance (NMR) is a powerful capability. From a series of tested molecules with affinity to metals, we chose to synthesize the well-characterized chelators EGTA and EDTA with carbon 13 moieties positioned directly at the metal-coordinating residues. We demonstrate that the metal-specific chemical

13 13

shifts exhibited by C-EGTA and "C-EDTA upon metal-coordination can be used to differentiate several biologically essential as well as toxic divalent metals. This feature enabled the quantification detection of the second messenger calcium in the presence of up to equimolar concentrations of magnesium e.g. in human serum. We furthermore show that ¹³ C-

13

EGTA and C-EDTA can be hyperpolarized by Dynamic Nuclear Polarization (DNP) to reach a several orders of magnitude higher signal-to-noise ratio to enable detection of micromolar concentrations of calcium and multiplexed metal detection by one-shot chemical shift imaging. The hyperpolarizable chemical shift sensors introduced here allow for the specific detection of several metals with high signal-to-noise in opaque biomedical or environmental samples.

Here, we report on generating hyperpolarizable C sensors for divalent metals in which the carbon 13 is incorporated directly into the coordination site of the chelators EDTA and EGTA to enable metal-specific detection of divalent metals via NMR and MRI spectroscopy with increased sensitivity. ¹³ C-enriched EDTA and EGTA were synthesized in two steps. Stepwise alkylation of l-2-diaminoethane/l,8-Diamino-3,6-dioxaoctane with ethyl bromoacetate-l- ¹³ C in acetonitrile afforded tetra-esters 1/2 respectively in good yield. The tetra- ¹³ C-acids, EDTA- ^1J C/EGTA- ^1J C, were obtained in quantitative amount by base hydrolysis of 1/2 at room temperature. By NMR analysis, we identified chemical shifts of the sensors (see Figure 1 and 7) in response to a range of divalent metals with known functions in cell signaling (calcium, magnesium and zinc) as well as metals with toxic effects (cadmium, arsenic and lead). ^A CEDIA exhibited a distinct chemical shift in response to all of these metals with line broadening observed in the presence of arsenic. C-EGTA on the other hand showed a large chemical shift in response to calcium (~10 ppm) whereas addition of magnesium caused line broadening; cadmium and Zinc induced similar chemical shifts of with apparent line broadening whereas no chemical shift was observed in the presence of arsenic.

We next assessed whether the metal- specific chemical shift would allow us to differentiate calcium in the presence of equimolar concentrations of magnesium. These two divalent metals exert distinct biological functions despite possessing very similar physical properties and appearing in similar intra- and extracellular concentrations which poses a substantial challenge for specific sensing by most methods. As can be seen in Figure 9, a titration curve was obtained up to one equivalent of calcium that is still linear in the presence of supersaturating concentrations of magnesium (Figure 9 B). The metal specificity allowed us to quantify calcium correctly in human serum that contained almost equimolar concentrations of magnesium (Figure 9 C).

To achieve NMR-based specific metal detection with increased sensitivity, we next subjected both ¹³ C-EGTA and ^{, 3} C-EDTA to DNP and obtained 15-20% of polarization levels. The resulting -10,000 fold signal enhancement allowed us to detect as low as 40 micromolar of calcium in a single acquisition (Figure 10 C). To further increase the signal from the hyperpolarized compound, we also synthesized the perdeuterated variant ^I3 C-EGTA-d8 which possesses a two-fold longer Ti of 25 seconds at 1 Tesla (Figure 10 D).

We next assessed how the two contrast agents could spatially resolve calcium distributions for multiplexed metal detection via chemical shift imaging (CS1). We thus positioned two NMR tubes concentrally inside a microimaging system containing the chemical shift sensors without and with saturating concentrations of calcium in the inner tube and conducted standard CSI imaging. Figure 1 1 shows the proton images (gray scale) with the area under the curve of the metal-bound (imier tube) or free chelator (outer tube) overlaid on a hot color scale (Figure 11 A). Whereas the CSI of the non-hyperpolarized contrast agents took many hours of scanning, the identical multiplexed measurement could be obtained in a single shot using hyperpolarized compound Figure 11 B).

- Discussion

13 13

We demonstrated how "C-EGTA and C-EDTA can be used as chemical shift sensors to differentiate several biologically relevant metals via NMR spectroscopy. The metal-specific chemical shift and the selectivity of ¹³ C-EGTA for calcium over magnesium afforded quantitative calcium detection in presence of equimolar concentrations of magnesium in biological fluids such as human serum (i.e. presence of additional biological compound such as proteins, lipids, sugars etc. do not interfere with the measurements) and multiplexed metal detection via chemical shift imaging. Hyperpolarization of the compounds resulted in an increase in signal-to-noise by a few orders of magnitude and thus allowed for detection of micromolar concentrations of calcium detected within a few second in a single acquisition and the large chemical shifts enable multiplexed metal differentiation by chemical shift imaging. Incorporating the carbon 13 directly at the metal coordination site allowed us to obtain chemical shifts that are specific for a particular metal. The narrow bandwidth NMR signal obtained for calcium indicates that there was a slow exchange (¾ < delta) between the free and calcium forms of the chelators on the NMR time scale at the field strengths used. In the case of ¹³ C-EDTA, the other tested metals were also observed to be in slow exchange which allowed for correction of variations in the concentration of the chemical shift agent by normalizing against the sum of the area under the curve. In the case of ^1J C-EGTA, magnesium coordination to ¹³ C-EGTA lead to strong line broadening and cadmium and zinc also generated considerable line broadening, indicating a faster metal exchange. For the detection of calcium in the presence of magnesium, the higher selectivity of C-EGTA for calcium as compared with ¹³ C-EDTA is reflected in the higher robustness of the binding curves of the former chemical shift sensor against competitive binding of magnesium as compared to C- EDTA.

- Summary

We have shown here how the carbon- 13 enriched chelators can be used for detection of divalent metals in two different modes of operation. The non-hyperpolarized compounds can be used to detect metals in the millimolar range that matches e.g. concentrations of calcium in serum that can deviate from the physiological range in e.g. endocrinological conditions such as hyperparathyroidism. In this regime, the relaxation rate is preferably short such that additional carbon- 13 enriched molecules such as, for instance, cell permeable esters may also be of interest for their good metal selectivity and ability to reach intracellular compartments of the samples. With hypeipolarization applied, much smaller concentrations of calcium can be detected and could also enable measurements of metal distribution in tissue.

The present invention provides specific chemical shift sensors designed and synthesized such that the nucleus is metal-specific, i.e. the identity of the metal can be detected by a change in the NM signal, e.g. a distinct change in the frequency of bandwidth. This is distinct from detecting the metal based solely on the sensitivity and specificity of the metal-coordinating agent as described in the prior art, such as in Smith et al , (1983) and US 2006/0193781 Al . Please see specifically Figure 7 C and D of the application. As shown in e.g. Figures 7 and 9, this metal-specific chemical shift enables specific detection of calcium by ¹³ C-EGTA and ¹³ C- EDTA in the presence of up to equimolar concentrations of the competing metal magnesium. This feature is enabled by positioning the carbon 13 to the metal-coordination site of ¹³ C- EGTA and ¹³ C-EDTA.

Furthermore, according to the present invention, the nucleus exhibiting the metal-sensitive chemical shift is hyperpolarizable. This is important for providing a few orders of magnitude more signal to noise which is essential in practice to achieve sufficient signal in a spatially resolved in vitro, ex vivo, or in vivo detection method (see specifically Figure 1 1). Although hypeipolarization can be achieved with ¹⁹ F, the relaxation rates of ¹⁹ F for the ones given for the BAPTA analogs, such as described in US 2006/0193781 Al , are too short to support any readout before signal decay occurs.

In summary, the present invention provides the use of metal-specific chemical shifts of hyperpolarizable nuclei within specially designed and selected metal-coordinating compounds. Designing and selecting compounds with suitable parameters of magnitude of chemical shift, bandwidth, relaxation rate, solubility, metal affinities is not obvious as demonstrated by the exemplary characterization of ^!3 C-EGTA and ¹³ C-EDTA and further compounds as shown in the Examples and Figures of this application. The following examples and drawings illustrate the present invention without, however, limiting the same thereto.

BRIEF DESCRIPTION OF THE DRAWINGS

Figure 1. Calcium detection with calcium-specific biosensors.

(A and B) Scheme depicting the structure and calcium-coordination of ¹³ C-EGTA and ¹³ C- EDTA. For further details, see Figure 7.

(C and D) ¹³ C NMR spectra for 1 mM ¹³ C-EGTA and ^,3 C-EDTA with addition of 0-1.5 mM calcium chloride in 15 mM MOPS with FI ₂ O/D ₂ O (1 : 1). Increasing concentrations of calcium result in a peak at -180 ppm with increasing amplitude (1 μΤ ¹³ C-methanol was used as an internal reference; measurements were taken at 310 K).

(E and F) Titration curves obtained from spectra in C and D. The Area under the Curve (AUC) was taken for the chemical shift corresponding to the bound calcium (-180 ppm) and normalized against the sum of the shifts corresponding to calcium-bound and calcium-free chelator (170.6 ppm and 174.5 ppm respectively). The apparent dissociation constant (KD) for ¹³ C-EGTA was 0.3489 mM (0.3314 mM to 0.3664 mM, 95% confidence intervals) 0,5278 mM (0,05863 mM to 0,9970 mM, 95% confidence intervals) for ¹³ C-EDTA

Figure 2. Calcium detection with calcium-specific biosensors in the presence of magnesium.

(A and B) Calcium titration curves obtained analogously to Figure 1 with 0.5 mM ¹³ C-EGTA

13 2+ and C-EDTA in calcium free artificial cerebrospinal fluid (aCSF) containing 0.7 mM Mg (0.5 iL ¹³ C-MeOH was used as an internal reference) (310 K, 500 MHz ( ¹³ C 125.83 MHz), pH 7.4). kD values were 0.3703 (0.3135 to 0.4272) for ¹³ C-EGTA and 0.4589 (0.3607 to 0.5571) for ¹³ C-EDTA.

Figure 3. Metal-specific chemical shifts.

1 mM calcium, magnesium or zinc were added to 1 mM (A) ^{] 3} C-EGTA and (B) ¹³ C-EDTA and resulted in distinct chemical shift for each metal (15 mM MOPS in H20/D20 (1 : 1), 0.5

1 ~

iL C-methanol was used as an internal reference; measurements were taken at 310 , 500 MHz ( ^I3 C 125.83 MHz), pH 7.4).

Figure 4. pH-dependence of the calcium sensors ' signal. (A) 1 niM ¹³ C-EGTA and (B) ^I3 C-EDTA in 15 mM MOPS buffer was adjusted to a pH range between 5 and 8. In half of the samples 1 mM calcium chloride was added. (0.5 μΕ ¹³ C- methanol was used as an internal reference), measurements at 310 , 500 MHz ( ¹³ C 125.83 MHz), pH 7.4).

(C) AUCs were computed for the peaks corresponding to calcium-free and calcium-bound compound respectively.

(D) The difference in ppm as compared with pH 5 is plotted for both calcium sensors. Figure 5. Molecular Structures of Metal Biosensors.

Scheme of the core structures (and their derivatives) of the metal sensors indicating the positions at which ^]3 C and ¹⁵ N, ²⁹ Si, ^{, 9} F, ⁸⁹ Y atoms can be introduced.

Modifications useful for bioconjugation or attaching chromophores, fluorophores or radioisotopes are enumerated as Ri _,2 . In Figures 5B-I, modifications of the metal-coordinating moieties that can alter affinities for metals are listed as options for Rl, ₂ . Possible perdeuterations to increase Tj times are indicated by the symbol X, photolabile moieties to influence the stability of the molecule as Y.

(A) core structures (B) EGTA and EDTA derivatives, (C) pyro-EGTA derivatives, (D) AATA derivatives, (E) APTRA derivatives, (F,G) BAPTA, HIDA and CGlu and β-ketone/crown ether derivatives, (H, I) mono-, di-, tri-pyridyl aniline/amine derivatives.

Figure 6. Selected Tj values at different field strengths.

Table 1 Metal Biosensor Properties

Name Formula MW T, (sec) T, (sec) Shift δ

(g/mol) @250 MHz @500 MHz ( pm)

EDTA ' ,„H, ₆ N > ₈ 292,24 (δ 170,696): (δ 174.79): 6.841 ± 2.1e- 5.2

13,086 ± 0.2e-2 2

+CaCl ₃ (1 : 1)(δ 179.98):

5.595± 1.2e-2

^,3 C-EDTA 296, 11 (δ 170,696): (δ 174.79): 6.841 ± 2.1e-2 5.2

13,086 ± 0.2e-2

EGTA <Γ _Η Η„Ν,0„ 380,35 (δ 170,245): (δ 170.34): 7.644 ± 2.3e- 9.8

15.00 ± 0.02e-2 2

+CaCL (1 : 1) (δ

180.13):5.481 ± 1.3e-2

¹³ C-EGTA 384.16 (δ 170,245): (δ 170.34): 7.644 ± 2.3e- 9.8 15.00 ± 0.02e-2 2

+CaCL (1 : 1) (6

180.13):5.481 ± 1.3e-2

¹³ C-EGTA- ' ,„'- -L¾N ₂ O ₁₀ 392.31 - - 9.8 d8

Br-Pyro- ¹² C„H _B BrN ₂ 0 507,287 (5179.394): 7,760 (6179.97): 4,524 0.8 EGTA ± l ,le-2 (6 147.84): 2.260 ± 2.2e-

2

(6 146.45): 2.395 ± 3.6e- 2

¹³ C-Br- 51 1,287 (6179.394): 7,760 (6179.97): 4,524 ± 2.6e-2 0.8 Pyro-EGTA ± l ,le-2

APTRA ^,3 C„H, ₃ N0 ₇ 283,234 (6 179.60): 3.879 ± 4.3e- 2

(6 177.1 1): 5.561 ± 7.3e- 2

(6 150.74): 1.340 ± 5.5e- 2

BAPTA 476,433 (6 178.86): 2.860 ± 1.5e- 0.3

2

(6 149.83): 2.160 ± 3.1e- 2

(δ 140.06): 5.090 ±

5.81e-l

+CaCL (6 178.56): 1.979

± 6.6e-2

HIDA 177,15 (6 170,306): 10,326 ± 0.3

0.6e-2

+CaCl ₂ (1 : 1 )(6 170,725):

3,484± 4,8e-2

Carboxy - ^,J C ₇ H,„0 ₆ 191 ,14 (6 178,385): 9,677 ±

Glutamate 8,5e-2

(CGIu) (6 177,944): 10,131±

9,9e-2

(6 174,593): 10,751±

9,3e-2

^,3 C-Glycine "C'C.HJSiO, 76,067 (6172,387): not determined not

24,768 ± 0.8e-2 determin ed

Glycine-1- 78,08 (6172,391): not determined not ¹³ CA2-d, 37,024 ± 0.6e-2 determin ed

Binding Affinities Name k|)-Ca k _D -Mg k _D -Zn k _D -Cu

F.DTA L09648E- 1 1 2,04174E-09 3, 16228E-17 1 ,58489E-19

I'vro- tbd. tbd. tbd. tbd.

EGTA

EGTA lE-1 1 6.30957E-06 1 ,25893E-13 1,99526E-18

APTRA 1.45E-03 l,80E-05 - -

BAPTA l ,07E-07 l ,70E-02 1 ,99526E-12 1 ,99526E-12

Figure 7. High sensitivity detection with hyperpolarized metal sensors.

13 13

Scheme depicting the coordination of divalent metals by C-EGTA (A) and C-EDTA (B). The gray circles on top of the carbon moieties indicate the position of the carbon 13 atoms. (C and D) Identification of various divalent metals by metal-specific chemical shifts of ^IS C- EGTA and ¹³ C-EDTA.

NMR spectra obtained from 2 mM ¹³ C-EGTA (C) and ¹³ C-EDTA (D) exhibiting distinct metal-specific chemical shifts in response to 2.2 mM of the biologically essential (Ca ²⁺ , Mg ²⁺ , divalent metals indicated above each spectrum. 15 mM

13

MOPS in H ₂ 0/D ₂ 0 (1 :1), 0.5 μΕ "C-methanol was used as an internal reference; measurements were taken at 310 K, 500 MHz ( ^I3 C 125.83 MHz), pH 7.4).

Figure 8. Multiplexed metal detection via chemical shift imaging.

Figure 9. Calcium detection with calcium-specific biosensors in the absence and presence of magnesium.

(A) Calcium titration curves obtained with EGTA (80 mM, natural abundance). (B) Titration of calcium with 0.5 mM ^I3 C-EGTA and ¹³ C-EDTA in calcium free artificial cerebrospinal fluid (aCSF) containing 0.7 mM Mg ²⁺ (0.5 ¹³ C-MeOH was used as an internal reference) (310 K, 500 MHz ( ¹³ C 125.83 MHz), pH 7.4).

13

(C) Titration of C-EGTA to determine the calcium concentration in human serum in the presence of magnesium. The inflection point indicates the concentration of calcium.

Figure 10. High sensitivity detection with hyperpolarized metal sensors.

13 13

"C-EGTA and C-EDTA were hyperpolarized by Dynamic Nuclear Polarization (DNP) and then analyzed by NMR (IT and 298 K) in the absence (top panel in A and B), and presence of half- saturating (middle panel) and saturating concentrations of Ca ²⁺ (bottom). NMR spectra were obtained each five seconds (FA=10 and TR=3000ms) and are plotted with an offset for better visibility.

(C) Hyperpolarization of ¹³ C-EGTA allows for detection of micromolar concentrations of calcium in a linear manner (inset). Panel (D) shows the deuterated version of ¹³ C-EGTA with half- saturating concentrations of calcium; the inset shows the signal decay for ¹³ C-EGTA and

1 ~

C-EGTA-d8 respectively. The dead-time between the end of polarization and start of the NMR measurement were 12 seconds. The corresponding spectrum is shown on the right.

Figure 11. Multiplexed metal detection via Chemical Shift Microimaging

(A) Two NMR tubes filled with non-hyperpolarized ¹³ C-EGTA or ⁱ³ C-EDTA were concentrically positioned inside the bore of a MR microimaging system with saturating calcium concentrations added to the inner tube. NMR spectra obtained from chemical shift images are overlayed on a proton FLASH image and areas under the curve (AUC) of the calcium-bound (left column) or free chelator (right column) are overlayed on a hot color scale. The corresponding spectra are shown on the right.

(B) Hyperpolarized "C-EGTA was dissolved into an NMR tube containing buffers with and without calcium prior to chemical shift imaging using a spatio spectral spiral sequence. MR images reconstructed at the specific frequencies of the calcium-bound or free chelator are overlayed in color on the grayscale FLASH sequence.

EXAMPLES

EXAMPLE 1

Materials and Methods 1.1 General

The chemicals and anhydrous solvents were purchased from commercial suppliers (Aldrich, Fluka, and VWR) and were used without further purification unless otherwise stated. Unless otherwise mentioned, all the reactions were carried out under an inert (nitrogen) atmosphere. All glassware was washed with a mixed acid solution and thoroughly rinsed with deionized, distilled water and pre-dried with a heat gun under vacuum. Ultra-pure deionized water (18 ΜΩ cm ^"1 ) was used throughout.

1.2 Chromatography.

Flash column chromatography was performed by using flash silica gel 60 (70-230 mesh) from Merck. Thin layer chromatography (TLC) was performed on aluminum-backed silica gel plates with 0.2 mm thick silica gel 60 F (E. Merck) using different mobile phases. The compounds were visualized by UV irradiation (254 nm), iodine and Dragondorff reagent staining.

1.3 Spectroscopy.

Each synthetic step was characterized by NMR and Mass. H and C NMR spectra were recorded on a Bruker 250 MHz and 500 MHz spectrometer (Ή; internal reference CDCI3 at 7.27 ppm or D ₂ 0 at 4.75 ppm; ¹³ C; internal reference CDCI3 at 77.0 ppm). All experiments were performed at 23 °C.

Electrospray mass spectra (ESI-MS) were recorded on SL 1 100 system (Agilent, Germany) with ion-trap detection in positive and negative ion mode. HRMS were measured on a Thermo Finnigan LQT.

1.4 Synthesis of chemical shift metal sensors.

(1) ¹³ C - labeled EGTA

f3 2-bis|carboxy("C)methyl](l ,14- ¹³ C ₂ )-6,9-dioxa-3,12-diazatetradecanedioic acid].

C -Labeled EGTA was synthesized in two steps as described in the literature (Ellis-Davies et ah). A solution of 2,2'-(ethane-l,2-diylbis(oxy))diethanamine (0.1 g, 0.68 mmol) and K ₂ C0 ₃ (0.56 g, 4.06 mmol) in anhydrous MeCN was stirred at room temperature for 30 min.

C - labeled ethyl bromoacetate-1 C (0.34 mL, 3.04 mmol) was added dropwise and the reaction mixture was heated at 80°C for 4 h. The reaction progress was monitored by TLC. Upon consumption of starting materials, the solvent was filtered through G-4 cintered funnel and solvent was removed under reduced pressure. The crude residue was purified by column chromatography (100 % DCM to 95:5 DCM/MeOH; R O.4) to give dimethyl 3, 12-bis(2- methoxy( ^I3 C)-2-oxoethyl)-6 _: 9-dioxa-3 2-diazatetradecane-l, 14-dioate(' ³ C) (0.295 g, 88%) as a yellow gum.

1H NMR (CDC1 ₃ , 250 MHz) d ppm: 1.24 (t, J-6 Hz, 12H), 2.94 (t, J=6 Hz, 4H), 3.42 - 3.70 (m, 16H), 4.13 (q, 1=7.0 Hz, 8H). ¹³ C NMR (CDC1 ₃ , 62.9 MHz) d ppm: 14.1, 53.6, 55.3, 56.2, 60.4, 70.1, 171.4. HR-MS (ES ⁺ ) m/z ¹² Ci ₈ ¹³ C ₄ H ₄ iN ₂ Oi ₀ requires 497.2895 [M+H] ⁺ ; found 497.2880 [M+H] ⁺ .

The tetra-acid (2-[(2-{bis[carboxy( ¹³ C)methyl]amino}ethyl)[carboxy( ^I3 C)methyl]amino](l- ¹³ C)acetic acid) was obtained by deprotection of the ethyl group on tetraethyl-2-[(2- {bis[carboxy( ¹³ C)methyl]amino}ethyl)[carboxy(' ³ C)methyl]amino](l- ¹³ C) acetate (0.6 g, 2.05 mmol) with NaOH (0.36 g, 9 mmol) in 10 mL MeOH: H ₂ 0 (9:1) for 2 h at room temperature. After the reaction was completed, the pH was adjusted to 7.4 by 3N HC1. The solvent was evaporated under reduced pressure to afford ¹³ C - labeled EDTA (0.435 g, 100% w/w) as an off-white solid.

1H NMR (D ₂ 0, 250 MHz) ) d ppm: 3.71 (s, 4H), 3.94 (d, J=4.5, 8H). ¹³ C NMR (D ₂ 0, 62.9 MHz) d ppm: 51.7, 58.5, 170.8. HR-MS (ES ⁺ ) m/z ¹² C ₆ ¹³ C ₄ H ₁₇ N ₂ 0 ₈ requires 297.1119 [M+H] ⁺ ; found 297.11 18 [M+H] ⁺ .

(2) ^I3 C - labeled EGTA-d8

[1,14-diethyl 3,12-bis[2-ethoxy-2-oxo( ² H ₂ )ethyl](2,2,13,13- H ₄ )-6,9-dioxa-3, 12- diazatetradecanedioate( ¹³ C ₄ )] .

¹³ C- ² H ₈ -Labeled EGTA was synthesized in similar way as compound 1 ( ¹³ C-Labeled EGTA). A solution of 2,2'-(ethane-l,2-diylbis(oxy))diethanamine (0.1 g, 0.68 mmol) and K ₂ C0 ₃ (0.56 g, 4.06 mmol) in anhydrous MeCN was stirred at room temperature for 30 min. Ethyl 2-bromo( ² H ₂ )acetate-l ¹³ C (0.38 mL, 3.14 mmol) was added dropwise and the reaction mixture was heated at 80°C for 4 h. The reaction progress was monitored by TLC. Upon consumption of starting materials, the solvent was filtered through G-4 cintered funnel and solvent was removed under reduced pressure. The crude residue was purified by column chromatography (100 % DCM to 95:5 DCM/MeOH; R =0.4) to give 1,14-diethyl 3,12-bis[2- ethoxy-2-oxo( ² H ₂ )ethyl](2,2,13,13- ² H4( ¹³ C))-6,9-dioxa-3, 12-diazatetradecanedioate (0.10 g, 29%) as a yellow gum.

1H NMR (CDCI3, 500 MHz) d ppm: 1.30 (t, J=7.00 Hz, 12H), 3.21 (t, J=4.50 Hz, 4H), 3.66 (t, J=5.0 Hz, 4H), 3.79 (s, 4 H), 4.22 (qd, J=7.00, 3.00 Hz, 8H). ¹³ C NMR (CDCI3, 126 MHz) d ppm: 14.0, 29.7, 53.4, 61.8, 68.1 , 69.6, 173.5. LR-MS (ES ⁺ ) m/z ^{I 2} Ci ₈ ^,3 C ₄ H37 ² H ₈ N ₂ 0,o requires 505.67 [M+H] ⁺ ; found 505.87 [M+H] ⁺ .

The tetra-acid (3,12-bis[carboxy( ¹³ C, ² H ₂ )methyl](2,2, 13, 13- ² H4( ¹³ C))-6,9-dioxa-3,12- diazatetradecanedioic acid) was obtained by deprotection of the ethyl group on 1 ,14-di ethyl 3,12-bis[2-ethoxy-2-oxo( ² H ₂ )ethyl](2,2, 13, 13- ² H ₄ )-6,9-dioxa-3, 12-

13

diazatetradecanedioate( C ₄ ) (0.1 g, 0.65 mmol) with NaOH (0.25 g, 3 mmol) in 10 mL MeOH: H ₂ 0 (9: 1) for 2 h at room temperature. After completion of the reaction, the pH was adjusted to 7.4 by 3N HC1. The solvent was evaporated under reduced pressure to afford ¹³ C- ² ¾-Labeled EGTA (0.077 g, 100% w/w) as an off-white solid.

1H NMR (D ₂ 0, 500 MHz) d ppm: 3.40 (t, J=5.00 Hz, 4H), 3.62 (s, 4 H), 3.80 (t, J=5.0 Hz, 4H). ^{i 3} C NMR (D ₂ 0, 126 MHz) d ppm: 38.8, 54.7, 64.7, 69.9, 170.4. LR-MS (ES ⁺ ) m/z ¹² C,o ¹³ C ₄ H ₂₁ H ₈ N ₂ 0 ₁₀ requires 393.39[M+H] ⁺ ; found 393.52 [M+H] ⁺ .

(3) ¹³ C-labeled EDTA

|2- |(2-{bis [carboxy( ¹³ C)metfayI] amino} ethyl) [carbosy( ¹³ C)methyl] amino] (l- ¹³ C)acetic acid].

A solution of ethane- 1,2-diamine (0.1 g, 1.67 mmol) and K ₂ CO3 (1.38 g, 10 mmol) in anhydrous MeCN was stirred at room temperature for 30 min. ^I3 C - labeled ethyl bromoacetate-1 ¹³ C (0.84 mL, 7.5 mmol) was added drop wise and the reaction mixture was heated at 80°C for 4 h. The reaction progress was monitored by TLC. Upon consumption of starting materials, the solvent was filtered through G-4 cintered funnel and solvent was removed under reduced pressure. The crude residue was purified by column chromatography (100 % DCM to 95 :5 DCM/MeOH; Rf=0.5) to give tetraethyl-2-[(2- {bis [carboxy( ¹³ C)methyl ] amino} ethyl) [ carboxy( ¹³ C)methyl] amino ](1- ¹³ C) acetate (0.625 g, 92%)) as a yellow gum. 1H NMR (CDCI3, 250 MHz) ppm: 1.28 (t, J=7.0 Hz, 12H), 2.92 (t, J=6.0 Hz, 4H), 3.61 (s, 8H), 4.17 (q, J=7.0 Hz, 8H). ¹³ C NMR (CDCI3, 62.9 MHz) ppm: 14.1, 51.4, 55.3, 60.4, 171.6. HR-MS (ES ⁺ ) m/z ¹² C ₁₄ ¹³ C4H ₃ 3N ₂ 0 ₈ requires 409.2371 [M+H] ⁺ ; found 409.2365 [M+H] ⁺ .

The tetra-acid (2- [(2- {bis [carboxy( ¹³ C)methyl] amino } ethyl) [carboxy( ¹³ C)methyl]amino] ( 1 - ¹³ C)acetic acid) was obtained by deprotection of the ethyl group on tetraethyl-2-[(2- {bis[carboxy( ¹³ C)methyl]amino}ethyl)[carboxy(' ³ C)methyl]amino](l- ^]3 C) acetate (0.6 g, 2.05 mmol) with NaOH (0.36 g, 9 mmol) in 10 mL MeOH: H ₂ 0 (9: 1) for 2 h at room temperature. After the reaction was completed, the pH was adjusted to 7.4 by 3N HC1. The solvent was evaporated under reduced pressure to afford ^{I 3} C - labeled EDTA (0.435 g, 100% w/w) as an off-white solid.

1H NMR (D ₂ 0, 250 MHz) ) d ppm: 3.71 (s, 4H), 3.94 (d, J=4.5, 8H). ^I3 C NMR (D ₂ 0, 62.9 MHz) d ppm: 51.7, 58.5, 170.8. HR-MS (ES ⁺ ) m/z ¹² C ₆ ¹³ C ₄ H ₁₇ N ₂ 0 ₈ requires 297.1 119 [M+H] ⁺ ; found 297.11 1 8 [M+H] ⁺ .

(4) Bromo derivative of ¹³ C-labeled Pyro-EGTA

[2-({2-[2-(2-{bis[carboxy( ¹³ C)methyl]amino}ethoxy)-5-bromophenoxy]ethyI}

[carboxy( ¹³ C)methyl]amino)(l- ¹³ C)acetic acid]

1

The bromo-derivative of C-labeled Pyro-EGTA was synthesized in 5 steps following a similar synthesis in the literature (Mishra et ah, 2011). The methyl groups were removed by using successive addition of borontribromide in the solution of 4-bromo-l,2- dimethoxybenzene in anhydrous C¾C1 ₂ at -4°C to room temperature for 2 h. The reaction was quenched by MeOH and solvent was evaporated under reduced pressure to afford 4- bromobenzene-1 ,2-diol. Stepwise alkylation of 4-bromobenzene-l ,2-diol with tert-b tyl 2- bromoethylcarbamate in anhydrous MeCN (6 h at 80°C) afforded compound di-tert-butyl 2,2'-(4-bromo-l,2-phenylene)bis(oxy)bis(ethane-2,l-diyl)dica rbamate, which was de-Boc by using 4N HC1. Dioxane solution (30 min at room temperature) to give 2,2'-(4-bromo-l,2- phenylene)bis(oxy)diethanamine in good yield.

A solution of 2,2'-(4-bromo-l ,2-phenylene)bis(oxy)diethanamine (0.1 g, 0.37 mmol) and K ₂ C0 ₃ (0.40 g, 2.91 mmol) in anhydrous MeCN was stirred at room temperature for 30 min.

13

Ethyl 2-bromoacetate-l C (0.185 mL, 1.64 mmol) was added drop wise and the reaction mixture was heated at 80°C for 4 h. The reaction progress was monitored by TLC. Upon consumption of starting materials, the solvent was filtered through G-4 cintered funnel and solvent was removed under reduced pressure. The crude residue was purified by column chromatography (100 % DCM to 95 :5 DCM/MeOH; Rf=0.55) to give tetramethyl 2-({2-[2-(2- {bis[carboxy( ¹³ C)methyl]amino}ethoxy)-5-bromophenoxy]ethyl} [carboxy( ^I3 C)m.ethyl] amino)(l- ¹³ C)acetate (0.18 g, 82%) as a yellow gum.

1H NMR (CDC1 ₃ , 250 MHz) d ppm: 1.25 (t, J=7.0, 12H), 3.05 - 3.33 (m, 4 H), 3.68 (d, J=5.0 Hz, 8H), 3.99 - 4.29 (m, 12H), 6.73 (d, J=9.0 Hz, 1H), 6.92 - 7.13 (m, 2H). ¹³ C NMR (CDC1 ₃ , 62.9 MHz) d ppm: 14.2, 53.5, 55.5, 56.4, 60.5, 1 12.8, 1 17.2, 1 17.6, 123.7, 145.7. 147.3, 171.4. HR-MS (ES ⁺ ) m/z ¹² C22 ¹³ C ₄ H ₄ oBrN ₂ 0,o requires 623.2001 [M+H] ⁺ ; found 623.1996 [M+H] ⁺ .

The tetra-acid [2-({2-[2-(2-{bis[carboxy( ^I3 C)methyl]amino}ethoxy)-5-biOinophenoxy] ethyl} [carboxy( ¹³ C)methyl]amino)(l- ^{! 3} C)acetic acid] was obtained by deprotection of the ethyl group on tetramethyl 2-({2-[2-(2- {bis[carboxy( ¹³ C)methyl]amino}ethoxy)-5- bromophenoxy]ethyl} [carboxy( ¹³ C)methyl]amino)(l- ¹³ C)acetate (0.15 g, 0.29 mmol) with NaOH (0.06 g, 1.46 mmol) in 10 mL MeOH: H ₂ 0 (9: 1) for 2 h at room temperature. After reaction completion, the pH was adjusted to 7.4 by 3N HC1. The solvent was evaporated under reduced pressure to afford ^{I 3} C-labeled m-Br-PyroEGTA (0.12 g, 100% w/w) as an off- white solid.

1H NMR (D ₂ 0, 250 MHz) ) d ppm: 3.02 (t, .1=5.0 Hz, 4H), 3.18 - 3.45 (m, 8H), 4.08 (t, J=5.0 Hz, 4H), 6.92 (d, J=8.50 Hz, 1H), 7.07 - 7.26 (m, 2H). ^I3 C NMR (D ₂ 0, 62.9 MHz) d ppm: 53.5, 58.3, 65.0, 1 12.4, 1 13.3, 1 15.2, 123.7, 146.6, 147.9, 179.4. HR-MS (ES ⁺ ) m/z ¹² Ci ₄ ¹³ C4H ₂₄ Bi-N ₂ Oio requires 51 1.0749 [M+H] ⁺ ; found 51 1.0746 [M+H] ⁺ .

(5) APTRA [A= 2,2'-(2-(carboxymethoxy)phenyIazanediyl)diacetic acid] and APTRA amide [B = 2,2'-(2-(2-morpholino-2-oxoethoxy)phenylazanediyl)diacctic acid].

Both compounds were synthesized in 4 steps as described in the literature (Often et al, 2001 , Dhingra et al). Alkylation of the tert-butyl 2-hydroxyphenylcarbamate with methyl bromoacetate (for A)/ 2-bromo-l -moipholinoethanone (for B) in anhydrous MeCN (6 h at 80°C) gave the corresponding ester and amide of A [methyl 2-(2-(tert- butoxycarbonylamino)phenoxy)acetate] and B [tert-butyl 2-(2-morpholino-2- oxoethoxy)phenylcarbamate] respectively. These intennediates were further treated with mild acid (4N HC1 Dioxane solution; (30 min at room temperature), cleaving the Boc group to afford the corresponding amines A [methyl 2-(2-aminophenoxy)acetate] and B [2-(2- aminophenoxy)-l-morpholinoethanone]. The ethyl di-esters of corresponding compounds A [diethyl 2,2'-(2-(2-methoxy-2-oxoethoxy)phenylazanediyl)diacetate] and B [diethyl 2,2'-(2-(2- morpholino-2-oxoethoxy)phenylazanediyl)diacetate] was obtained by alkylation with ethylbromoacetate in anhydrous DMF using proton sponge as strong base (48 h at 80°C). Following basic hydrolysis of these esters afforded resultant acids (A and B). After reaction completion, the pH was adjusted by 3N HC1. The solvent was evaporated under reduced pressure to afford (A and B) as dark yellow solids.

1.5 NMR-based metal detection of non-hyperpolarized compounds

All NMR experiments with metal chelators described herein were performed at the Department of Chemistry of Technische Universitat Munchen (TUM) on a Bruker AV500 500 MHz Nuclear Magnetic Resonance Spectrometer equipped with a cryoprobe. pH values were measured with a standard pH electrode.

All solutions were prepared in MOPS buffer (30 mM) and deuterated water in a ratio of 1 : 1 , at pH 7.4 and were measured at 300K. ¹³ C-methanol was used as a ¹³ C reference.

A thermal spectrum was acquired (number of scans (ns) 1000, number of points (np) 16) using a 30° pulse and 90 degree pulse for decoupling. ^I3 C Tj values were calculated from a fit to a series of spectra acquired with varying repetition times (from 0.01 s to 50 s). The assignment of the NMR-peaks of all compounds was done using NMR prediction software (ChemSketch - ACDLABS 12.0) and standard ID and 2D-NMR-spectroscopy. Measurements were taken at 24°C, 500 MHz (13C 125.83 MHz), pH 7.4) in 15 mM MOPS with H ₂ 0/D ₂ 0 (1 :1), 1 μΐ. ' ³ C-methanol was used as an internal reference.

13 13

1.6 Dynamic Nuclear Polarization of C-EGTA and C-EDTA and NMR detection

The samples were prepared dissolving 4.2 mg of trityl radical (0X063, GE-Healthcare, Amersham UK) with 100 ih of 0.5 M of EGTA (or EDTA) solution (DMSO/D20) and a trace amount of Dotarem (Guerbet, Birmingham UK).

The samples were polarized via dynamic nuclear polarization on a HyperSense DNP polarizer system (Oxford Instruments Molecular Biotools, Oxford, UK) using 60-100 min of microwave irradiation at 1.3 K and 3.35 T. The polarized samples were dissolved in a heated and pressurized solution of 100 mM MOPS buffer prepared in D ₂ 0/DMSO-d6 (10: 1) with or without CaCl ₂ , leading to a 13 mM solution of the hyperpolarized substrate with a pH of approximately 7.4.

7. 7 Chemical Shift Imaging of ¹³ C-EGTA and ¹³ C-EDTA at equilibrium polarization 200 mM ^{, 3} C-EDTA or ^{, 3} C-EGTA in 200 mM MOPS in D ₂ 0 buffer pH 7.4. Calcium was added to one tube at 300 mM. Microimaging was performed on a Bruker WideBore UltraShield 500WB PLUS with Avance3HD Console and Great60 - 60A Gradient Amplifiers. The instrument was equipped with Micro 5 gradient system (5G/cm/A -> 300G/cm = 3T/M), BLAX500 - 500W rf power amplifier, and 5mm double tuned 1H/13C coil.

The data were analyzed using ParaVision 6.0, TopSpin 3.2, and CSI tool software developed by Magnetic Resonance at the Dept. of Molecular Cardiology (Dusseldorf University).

1.8 Chemical Shift Imaging of hyperpolarized C-EGTA and ¹³ C-EDTA

Chemical Shift Imaging of the hyperpolarized substances was carried out on a 7T small animal scanner (Allied Technologies) using a spectral-spatial spiral sequences (Wiesinger et al., 2012)

The features disclosed in the foregoing description, in the claims and/or in the accompanying drawings may, both separately and in any combination thereof, be material for realizing the invention in diverse forms thereof.

REFERENCES

Angelovski, G., Chauvin, T., Pohmann, R., Logothetis, N. K., & Toth, E. (2011). Calcium- responsive paramagnetic CEST agents. Bioorganic & Medicinal Chemistry, 19(3), 1097— 1105. doi: 10.1016/j.bmc.2010.07.023

Ardenkjaer-Larsen, J. H., Fridlund, B., Gram, A., Hansson, G., Hansson, L., Lerche, M. H., et al. (2003). Increase in signal-to-noise ratio of > 10,000 times in liquid-state NMR. Proceedings of the National Academy of Sciences of the United States of America, 700(18), 10158-10163. Atanasijevic, T., Shusteff, M., Fam, P., & Jasanoff, A. (2006). Calcium-sensitive MRI contrast agents based on superparamagnetic iron oxide nanoparticles and calmodulin. Proceedings of the National Academy of Sciences of the United States of America, 103(40), 14707-14712. doi: 10.1073/pnas.0606749103

Bar-Shir, A. et al. Metal Ion Sensing Using Ion Chemical Exchange Saturation Transfer (19)F Magnetic Resonance Imaging (2013). J Am Chem Soc. doi:10.1021/ja403542g

Amnon Bar-Shir; Nirbhay Yadav; Assaf A. Gilad; Peter C. van Zijl; Michael T. McMahon; Jeff W. Bulte. Poster, WMIC 2014, 19F probe allows simultaneous detection of multiple metal ions using iCEST MRI

Caravan, P. (2006). Strategies for increasing the sensitivity of gadolinium based MRI contrast agents. Chemical Society Reviews, 35(6), 512-523. doi: 10.1039/b510982p

Carter, . P., Young, A. M., & Palmer, A. E. (2014). Fluorescent Sensors for Measuring Metal Ions in Living Systems. Chemical Reviews, 114(8), 4564-4601. doi:10.1021/cr400546e

DeGraaf, Robin. In Vivo NMR Spectroscopy: Principles and Techniques, John Wiley & Sons; 2007.

Durham, A. C. II., & Walton, J. M. (1983). A survey of the available colorimetric indicators for Ca2+ and Mg2+ ions in biological experiments. Cell Calcium, 4(1), 47-55. doi:10.1016/0143-4160(83)90048-9.

Ellis-Davies, G. C. R. (2008). Neurobiology with Caged Calcium. Chemical Reviews, 108(5), 1603-1613. doi: 10.1021/cr078210i

Ernst, Richard. Principles of Nuclear Magnetic Resonance in One and Two Dimension (International Series of Monographs on Chemistry), Oxford University Press; 1997.

Henry, P.-G., Marjanska, M., Walls, J. D., Valette, J., Gruetter, R., & U urbil, K. (2006). Proton-observed carbon-edited NMR spectroscopy in strongly coupled second-order spin systems. Magnetic Resonance in Medicine : Official Journal of the Society of Magnetic Resonance in Medicine / Society of Magnetic Resonance in Medicine, 55(2), 250-257. doi:10.1002/mrm.20764

Jindal, A. K., Merritt, M. E., Suh, E. H., Malloy, C. R., Sherry, A. D., & Kovacs, Z. (2010). Hyperpolarized 89Y complexes as pH sensitive NMR probes. Journal of the American Chemical Society, 132(6), 1784-1785. doi: 10.1021/ja910278e

Looger, L. L. (2013). Genetically encoded calcium indicators for multi-color neural activity imaging and combination with optogenetics, 1-29. doi: 10.3389/fnmol.2013.00002/abstract

Mishra, A., Logothetis, N. K., & Parker, D. (201 1). Critical In Vitro Evaluation of Responsive MRI Contrast Agents for Calcium and Zinc. Chemistry - a European Journal, 17(5), 1529- 1537. doi: 10.1002/chem.201001548

Nelson SJ, Ozhinsky E, Li Y, Park I, Crane J. Strategies for rapid in vivo 1H and hyperpolarized 13C MR spectroscopic imaging. J Magn Reson 2013 ;229: 187-97.

Nelson SJ, Kurhanewicz J, Vigneron DB, Larson PE, Harzstark AL, Ferrone M, van Criekinge M, Chang JW, Bok R, Park I, Reed G, Carvajal L, Small EJ, Munster P, Weinberg VK, Ardenkjaer-Larsen JH, Chen AP, Hurd RE, Odegardstuen LI, Robb FJ, Tropp J, Murray JA. Metabolic Imaging of Patients with Prostate Cancer Using Hyperpolarized [1 - ¹³ C]Pymvate. Sci Trans Med. 2013 Aug 14;5(198): 198ral08.

Nonaka, H., Hata, R., Doura, T., Nishihara, T., Kumagai, K., Akakabe, M., et al. (2013). A platform for designing hyperpolarized magnetic resonance chemical probes. Nature Communications, 4, 1-7. doi: 10.1038/ncomms3411

Ntziachristos, V. (2010). Going deeper than microscopy: the optical imaging frontier in biology. Nature Methods, 7(8), 603-614. doi:10.1038/nmeth.l483

Otten, P. A., London, R. E., & Levy, L. A. (2001). A new approach to the synthesis of APTRA indicators. Bioconjugate Chemistry, 12(1), 76-83. Perez, J. M., Josephson, L., O'Loughlin, T., Hogemann, D., & Weissleder, R. (2002). Magnetic relaxation switches capable of sensing molecular interactions. Nature Biotechnology, 20(8), 816-820. doi: 10.1038/nbt720

Que, E. L., & Chang, C. J. (2010). Responsive magnetic resonance imaging contrast agents as chemical sensors for metals in biology and medicine. Chemical Society Reviews, 39(1), 51- 60. doi:10.1039/B914348N

V. Rieke, K. Vigen, G. Sommer, B. Daniel, J. Pauly, K. Butts, Referenceless PRF Shift thermometry, MRM, 2004 Jun;51 (6): 1223-31.

Robitaille, P. M., & Jiang, Z. (1992). New calcium-sensitive ligand for nuclear magnetic resonance spectroscopy. Biochemistry, 31(50), 12585-12591. doi:10.1021 bi00165a007

F A Schanne, T. L. D. R. K. G. J. F. R. (1990). Development of 19F NMR for measurement of [Ca2+]i and [Pb2+]i in cultured osteoblastic bone cells. Environmental Health Perspectives, 84, 99.

Shapiro, M. G., Atanasijevic, T., Faas, H., Westmeyer, G. G., & Jasanoff, A. (2006). Dynamic imaging with MRI contrast agents: quantitative considerations. Magnetic Resonance Imaging, 24(4), 449-462. doi: 10.1016/j.mri.2005.12.033

Smith, G. A., Hesketh, R. T., Metcalfe, J. C, Feeney, J., & Morris, P. G. (1983). Intracellular calcium measurements by ¹⁹ F NMR of fluorine-labeled chelators. Proceedings of the National Academy of Sciences of the United States of America, 80(23), 7178-7182.

Steenbergen, C, Murphy, E., Levy, L., & London, R. E. (1987). Elevation in cytosolic free calcium concentration early in myocardial ischemia in perfused rat heart. Circulation Research, 60(5), 700-707. doi: 10.1161/01.RES.60.5.700

Verma, K. D., Forgacs, A., Uh, H., Beyerlein, M., Maier, M. E., Petoud, S., et al. (2013). New Calcium-Selective Smart Contrast Agents for Magnetic Resonance Imaging. Chemistry - a European Journal, 19(52), 18011-18026. Viale, A. et al. Hyperpolarized agents for advanced MRI investigations (2009). Q. J. Nucl. Med. Mol. Imaging 53, 604-617 .

Viale, A. & Aime, S. (2010). Current concepts on hyperpolarized molecules in MRJ. Current Opinion in Chemical Biology 14, 90-96.

Wiesinger, F., Weidl, E., Menzel, M. I., Janich, M. A., Khegai, O., Glaser, S. J., Haase, A., Schwaiger, M., and Schulte, R. F., "IDEAL spiral CSI for dynamic metabolic MR imaging of hyperpolarized [1-13C] pyruvate," Magnetic Resonance Medicine 68, 8-16 (2012).

Winer, J. L., Liu, C. Y., & Apuzzo, M. L. J. (2012). The use of nanoparticles as contrast media in neuroimaging: a statement on toxicity. World Neurosurgery, 75(6), 709-711. doi: 10.1016/j.wneu.201 1.08.013