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Hyperpolarized (HP) tracers dramatically increase the sensitivity of magnetic resonance imaging (MRI) to monitor metabolism non-invasively and in vivo. Their production, however, requires an extra polarizing device (polarizer) whose complexity, operation and cost can exceed that of an MRI system itself. Furthermore, the lifetime of HP tracers is short and some of the enhancement is lost during transfer to the application site. Here, we present the production of HP tracers in water without an external polarizer: by Synthesis Amid the Magnet Bore, A Dramatically Enhanced Nuclear Alignment (SAMBADENA) is achieved within seconds, corresponding to a hyperpolarization of ~20%. As transfer of the tracer is no longer required, SAMBADENA may permit a higher polarization at the time of detection at a fraction of the cost and complexity of external polarizers. This development is particularly promising in light of the recently extended portfolio of biomedically relevant para-hydrogen-tracers and may lead to new diagnostic applications.
Within the past decades, magnetic resonance imaging (MRI) has become an indispensable tool for medical diagnostics. Because of its low sensitivity, however, the only nucleus used in clinical routine is hydrogen (1H), which is the most abundant element in vivo (~80M) and holds the greatest gyromagnetic ratio of all stable nuclei (42 × 2πMHzT−1). But even for 1H, the polarization, which is the fraction of all spins contributing to the MR signal, does not exceed 3p.p.m. in a magnetic field of 1T. All other stable nuclei have a lower polarization and much lower abundance in vivo.
Still, the need for a non-invasive tool for chemical analysis in vivo, for example to measure the metabolism and treatment response of tumors1, is great. It appears that this need is precisely met by magnetic resonance (MR) spectroscopy, which is very successful for chemical analysis in vitro. However, low sensitivity makes its use in clinical routines very limited2. Nuclear hyperpolarization (HP) promises to overcome this hurdle and has enabled MR signal enhancement by several orders of magnitude3. The MR signal of most X-nuclei (nuclei other than protons) in vivo is low and thus both distribution and metabolism of magnetically labelled or hyperpolarized X-nuclei can be observed without significant background, similar to positron emission tomography. The first human studies of this method have shown very promising results4,5 and more are underway.
The most prominent techniques for the production of hyperpolarized 13C-tracers are dissolution dynamic nuclear polarization (dDNP)6 and parahydrogen (pH2) and synthesis allows dramatically enhanced nuclear alignment (PASADENA)7, also known as pH2-induced polarization (PHIP)8. dDNP achieves liquid-state polarization by transferring polarization from electrons to nuclei in the solid state at a temperature of a few K and in a strong magnetic field of a few T, followed by rapid dissolution. PHIP, in contrast, is the only technique to date that allows polarization to take place in the liquid state, either by hydrogenation7 or reversible exchange with pH2 (ref. 9). While dDNP is the only technique commercially available and used for human applications, it is associated with rather high cost, a relatively low output and long polarization cycles, although many promising attempts are being pursued to overcome these shortcomings10,11,12. PHIP, in contrast, is more cost efficient, very fast and requires less hardware. A hitherto substantial drawback of this technique—its limited portfolio of tracers—may have been overcome by the discovery of new agents13,14,15 and side-arm hydrogenation PHIP (PHIP-SAH), which has enabled the polarization of acetate and pyruvate16. Both methods share the disadvantage that the HP-tracer has to be produced in a dedicated polarizing device (polarizer) outside of the MRI system3,6,17,18,19,20,21,22,23,24,25,26,27,28,29. During the ensuing transfer through varying magnetic fields to the application site, inevitably, some of the polarization is lost to the T1 decay towards thermal equilibrium.
Here, we present a new method that achieves 13C-HP in excess of 20% in aqueous solution within seconds in the bore of a commercial MRI system. No external polarizer is needed—the only items that are required, in addition to an MRI scanner, are pH2, a reaction chamber, some valves and a digital output to control the process. By Synthesis Amid the Magnet Bore, A Dramatically Enhanced Nuclear Alignment (SAMBADENA) is obtained. By producing a sterile HP-tracer in situ, within the bore of an MRI, at the application site and at high field, this new method addresses some of the aforementioned shortcomings of dDNP and PHIP.
A maximum theoretical polarization yield of 48.7% was simulated for 1-13C hydroxyenthyl-propionate (HEP), a tracer that was previously used for in vivo angiography27,30. The corresponding evolution intervals for the spin-order-transfer (SOT) sequence l-PH-INEPT+ (longitudinal-para-hydrogen-insensitive nuclei enhancement by polarization transfer) were t1=69.8ms and t2=38.9ms (total 108.7ms). Several other polarization maxima were found but required longer evolution intervals (Fig. 1). The polarization yield was found to be relatively stable with respect to errors of J-couplings, pulses and evolution times (Fig. 1).
Experimentally, HP was produced within an MRI system by using the available hardware of the system itself (Fig. 2). The signal that was directly produced by the PH-INEPT+ sequence was quantified and corresponded to a nuclear polarization of P=24%, approximately half of the theoretical maximum. This polarization level corresponds to an enhancement factor of η≈40,000 for 13C at 7T (hydrogenation time th=4s, 5.54mM HEP in H2O; Fig. 3).
The inter-day yield and reproducibility of SAMBADENA was quantified in nine experiments to P≈(21±2) % with 5.54mM HEP in H2O (Fig. 4).
While a polarization of the order of few per cent is sufficient for biomedical use3,31, the short-lived transversal polarization generated by the PH-INEPT+ sequence is not suited for in vivo application—longitudinal magnetization is required instead. As predicted by Bär et al.32, the l-PH-INEPT+ sequence enabled the production of longitudinal magnetization hyperpolarized to a similar level, P=(19±2) % (detected 2s after generation, for 5.54mM HEP in D2O) (Fig. 5). This magnetization decayed much slower with T1 (instead of T2) and enabled other experiments as described in the following.
The T1 of HEP dissolved in D2O was measured to (79±2) s at 7T (Fig. 5), which is more than the 70s reported at 4.7T (ref. 26). In degassed and deionized H2O, the T1 of HEP at 7T was measured to (75±5) s, which is less than (101±7) s reported at 48mT (ref. 19). These long relaxation times are advantageous with respect of the further use of the tracer. If, for example, 20s were to be used for the injection of the tracer in vivo, only about one fifth of the initial polarization would be lost.
As expected and reported before18, the hydrogenation time had a strong impact on the HP yield: the highest polarizations were observed between th=4–8s (Fig. 6). Note that considerable polarization, about half of the maximum, was observed after hydrogenation periods th as long as 15s. The slow decay is likely attributed to the decay of the para-order of the hydrogens that were added to the tracer. Note that no refocusing or decoupling pulses were applied during th.
The apparent build-up hydrogenation time constant of the catalysis (Tcat) and para-order relaxation constant (Tpara) were estimated to Tcat=(1.6±0.9) s and Tpara=(16±6) s, respectively, by fitting a model to the experimental data (equation (2) in Methods). The onset of the hydrogenation reaction (t0) extracted from the fit was t0=(1.0±0.5) s. This value reflects the finite time required for the hydrogen being delivered to the reactor, to enter the solution, to build-up pressure and to start the reaction. It is supported by a high-speed video of the hydrogenation reaction, where the bubbling came to a stop ~1s after the injection, indicating an equilibration of the pressure (Supplementary Movie 1). Disregarding the contribution of relaxation, the asymptotic maximum polarization level extracted from the fit was (27±5) % (goodness of the fit: R2=0.7, concentrations of HEP and catalyst of cHEP=5.5mM and ccat=2.1mM). The deviation to the theoretical maximum may be attributed to noise in the data, relaxation before and during the SOT-sequence itself or experimental imperfections.
This data indicates that after th=4s, (85±18) % of all molecules are hydrogenated. Since 100% hydrogenation is assumed for the quantification of the polarization yield, it is likely that the reported polarization is underestimated. Note that Tcat, Tpara, maximum polarization level and the optimal th are expected to be dependent on concentrations of the precursor and catalyst.
For any biomedical application, highly concentrated, highly hyperpolarized samples are needed to achieve sufficient signal. By variation of th, the catalyst concentration (ccat) and reaction pressure (p), the polarization achieved for 80mM tracer was increased from 3.4 to 7.1% and eventually~13% (Table 1 and Supplementary Fig. 1). It must be noted, though, that the last measurement could not be repeated because the pressure exceeded the specifications of the current instrumentation and caused damage to the equipment. In addition, P≈17% was readily achieved in a sample of 22mM, 3.5cm off the isocentre of the magnet.
To demonstrate the feasibility of simultaneous HP and MRI, HEP was hyperpolarized by SAMBADENA within seconds, injected into a rat post mortem and 13C-MRI was acquired (rattus rattus, 7 days old). The rat was placed next to the reaction chamber and positioned in the sensitive volume of the coil within the magnet (Fig. 7a,b). In contrast to all other experiments, in this setting, the reaction chamber was not in the isocentre, but at a distance of 3.5cm along the z axis of the magnet. At this position, the SOT sequence was still efficient, as demonstrated by an HP of 17% that was achieved for 22mM HEP in 700μl aqueous solution in the reactor (Table 1).
For ex vivo MRI, a catheter was connected to the outlet of the reaction chamber and inserted into the thorax of the rat. The HP-experiment was repeated and ~330μl of the hyperpolarized tracer were injected through the catheter into the rat without leaving the magnet. Sub-second 13C-MRI was acquired and strong, hyperpolarized signal was observed (Fig. 7c). The co-registration with a T2-weighted 1H-MRI (Fig. 7d,e) showed that the 13C-signal was localized around the heart of the animal and within the reaction chamber, with a maximum 13C-signal-to-noise ratio (SNR) of 113 and 111, respectively (Supplementary Fig. 2 and Supplementary Table 1). In the same scan, the SNR in the model solution was quantified to 9. A Zero-Echo-Time (ZTE) MRI33 was acquired afterwards to depict the entire setup (Fig. 7f).
SAMBADENA enables the HP of 13C-labelled tracers to high levels, in aqueous solution, within seconds and within the magnet bore next to the application site. For the first time, high 13C-HP was achieved without a dedicated polarizer—the hardware of an MRI system was used instead. This method circumvents some of the shortcomings that are associated with current 13C-HP methods, foremost the need of a dedicated, expensive and complex external polarizer and lengthy transfer of the sample. Other challenges persist and are discussed in the following.
Obtaining a pure solution devoid of the catalyst is a persisting challenge for all pH2-based HP methods, although strong progress was reported recently by using either heterogeneous catalysts34,35,36,37 or a biphasic approach38. The latter appears to be particularly promising with respect to the implementation in the presented setup, and heterogeneous catalysts are currently being investigated in our laboratory.
Whereas other HP methods require an extra polarizer device whose complexity, operation and cost can exceed that of the MRI scanner itself, the additional equipment needed here is very little. The only extra component that is needed inside the magnet is a reaction chamber. In the experiments presented here, the bulk reactor occupies less than one-third of the imaging field of view (FOV). A significant reduction in size appears feasible because the actual inner volume of the reactor is less than 1/100 of the FOV (2cm3 versus 342cm3). The only requirement for the MRI system is a 13C channel, which is necessary for 13C-MRI in general.
A relatively large volume transmitter is advantageous to enable simultaneous application of the SOT and MRI sequence. A dedicated pickup coil at the region of interest (ROI) may assure a high sensitivity while the homogeneous excitation of the large volume coil (covering both chamber and animal) would be maintained. To improve the accuracy of the applied pulse sequences, two different shim settings were used; one for the HP and one for the imaging.
SAMBADENA may be simplified further by using the digital outputs of the MRI system to control the valves; its implementation on any commercial multinuclear MRI system appears feasible. Other pH2-based approaches are much less cost intensive than dDNP, but still require an external polarizer device with the associated cost and complexity17,18,19,21,22,23,26,27,29,29.
While the actual HP process is executed with a single button, the production of pH2 and precursor solution requires some training. In the future, both pH2 and solution may be prepared elsewhere and shipped to the application site. At this stage, the catalyst–substrate solution is filled manually into the reactor outside the scanner. We envision that future implementations will feature in-bore loading, automatic heating and likely automated injection18.
Any preparation of the hyperpolarized tracer, such as cooling or quality control, would take place at the elevated field of the host MRI system where the T1 is long (here:~80s). Note, however, that any human application would require fast and comprehensive testing of the solution before injection, to ensure the safety of the patient, which is challenging especially in the magnet bore.
The HP levels reached −~20% for a tracer concentration of 6 and 22mM, and 13% for 80mM—are likely sufficient for a meaningful in vivo application, in particular because no lengthy transfer of the tracer through varying magnetic fields is necessary.
The SOT-sequence l-PH-INEPT+ was implemented for the first time, and about half of the theoretically achievable polarization yield was observed (P=(19±2) %). Other sequences with a higher theoretical yield appear feasible and may improve the polarization as well.
Fast hydrogenation at elevated temperature and high pressure was found to be essential for a high polarization (Fig. 2 and Supplementary Fig. 1). The catalytic hydrogenation time constant extracted from experimental data indicated that (85±18) % of a 5.5mM precursor solution were hydrogenated after a 4s reaction at 15bar and~80°C. Especially with respect to a high substrate concentration, an even higher pressure and temperature is expected to improve the yield further (see Supplementary Fig. 1).
Polarization losses may be attributed to relaxation before, during and after the polarization transfer, imperfect pulses, timings (or erroneous J-coupling constants) and incomplete hydrogenation. We observed that the reaction chamber distorted the line shape of a model solution, which may also cause polarization loss (see Supplementary Figs 3 and 4). Note that 100% hydrogenation and pH2 enrichment was assumed for the quantification, which results in some underestimation of the reported polarization.
The technical feasibility of using the MRI simultaneously for the HP and subsequent imaging was demonstrated by an ex vivo experiment (Fig. 7). Although there appears to be no fundamental hurdle for a preclinical in vivo application, the following aspects have to be taken into account: First, the equipment to support the animal (anaesthesia, vital sign monitoring, heating) have to fit into the bore along with the animal and the reactor. This issue may be addressed by employing a smaller reactor designed to be used with a commercial animal bed. Second, the injection needs to be well controlled regarding flow, pressure and total volume. An automated injection system for dDNP that was already described and evaluated positively in many in vivo experiments39 may be used here. Third, unwanted heating of the animal (by the reactor) should be avoided, and the HP-solution needs to be cooled to temperature that is acceptable for injection. This first implementation was not designed with an in vivo demonstration in mind, but the temperature at the position of the animal is close to the required range (measured as 42 to 37°C as a function of distance from the outside wall of the reactor, see Supplementary Fig. 5). The temperature at the position of the animal may be reduced further by adding insulation and/or using a different method of heating. As for the temperature of the solution, an elevated temperature is required only at the time of the hydrogenation (to provide fast catalysis, a high polarization yield and sterilize the tracer solution, see Supplementary Note 1). The temperature of the tracer exiting the catheter used in vitro was measured to (43±3)°C and was further reduced to (32±3)°C by guiding the catheter through iced water (Supplementary Table 2). Thus, it appears feasible to reach an acceptable temperature within seconds. Current work focuses on adapting SAMBADENA for the HP of biomolecules to conduct metabolic studies in vivo.
A major limitation of pH2-based methods was the hitherto restricted portfolio of relevant tracers. However, this hurdle may have been overcome by the HP of pyruvate and acetate16, phospholactate13,14,15, and (diethyl-) succinate1,40,41,42,43 with pH2. Current work focuses on adapting SAMBADENA to these tracers.
Compared with other methods, the HP of a liquid-state tracer next to the application site may enable the delivery of higher polarization in vivo at the time of detection, especially for agents with short relaxation time T1 (such as glucose), and enable better resolution of metabolites with hitherto low SNR.
Given its simplicity, its high polarization yield, fast production and low cost, SAMBADENA may have an important impact on the research of HP tracers, which hold the potential to revolutionize the use of MRI in modern diagnostics.
pH2 was enriched to ~95% similar as descried previously and stored in aluminium bottle to be used on demand44.
Measurements were performed using a 7T preclinical small animal MRI system (Biospec 7/20, PV5.1, Bruker, Germany), using a dual-resonant 1H–13C transmit-receive volume coil (Rapid, Germany; Fig. 2).
A reaction chamber with an inner volume of ~2ml was custom-made from polysulfone (PSU 1000) to allow a high hydrogenation temperature (~80°C) and pressure (~15bar). Tubes were connected to the inlet at the bottom (1/8” × 1/16”, PTFE, SCP GmbH, Germany) and outlet at the top (1/16” × 0.75mm, PTFE, SCP GmbH, Germany) to inject and release pH2, respectively. Both tubes were connected to magnetic valves (type 0124, Bürkert, Germany) outside of the MR system. The valves were controlled by a custom-written software (MATLAB, MathWorks, USA) using the digital outputs of a data acquisition board (DAQ 6125, National Instruments, USA). A second reactor was used for hydrogenation experiments (Fig. 6) and ex vivo MRI experiments, where an additional outlet at the bottom served to inject the tracer into the animal (Fig. 7).
A rhodium-based catalyst was prepared fresh by mixing a biphosphine ligand (1,4-bis-[(phenyl-3-propane sulfonate) phosphine] butane disodium salt, Q36333, MW=562.53gmol−1, Sigma Aldrich, MO, USA) with a rhodium complex (bis(norbornadiene)rhodium (I) tetrafluoroborate, MW=373.99gmol−1, CAS 36620-11-8, StremChemicals, MA, USA) in degassed D2O (Deuterium oxide, 99.9 atom % D, CAS 7789-20-0, Sigma Aldrich, MO, USA) or degassed and deionized H2O (ref. 17).
1-13C, 2,3,3-2H3-hydroxyethyl-acrylate (HEA, 99% 13C, MW=120.13g mol−1, CAS: 1216933-17-3, Sigma Aldrich, USA) was added to the solution. During the HP experiment, pH2 was added to HEA and 1-13C, 2,3,3-2H3-HEP was formed (Fig. 8).
To achieve a high hydrogenation temperature, but to avoid degeneration of the catalyst18, a stock solution containing catalyst and substrate at high concentrations was prepared and kept at room temperature (concentrations: crhodium=21mM, cligand=23mM, cHEA=55.4mM). The reaction chamber was heated in a water bath to ~90–95°C. Shortly before the experiment, one part (100μl) of the stock and nine parts of hot H2O or D2O (~90°C) were filled into the reaction chamber and placed in the MRI scanner. Unless otherwise indicated, the final concentration was 2.1mM for the catalyst (with 10% excess of the ligand) and 5.54mM of HEA.
For the experiment with elevated tracer concentrations, the required amount of HEA was added to the reactor afterwards (for example 9mg to reach 80mM in 1ml solvent).
This procedure permitted obtaining a high hydrogenation temperature of >80°C, while keeping the catalyst at room temperature for most of the time18.
Both PH-INEPT+ (ref. 45) and l-PH-INEPT+ (ref. 31) sequences were implemented on the MRI system. The PH-INEPT+ sequence, which consists of three excitation pulses (45°y-1H, 90°y-1H and 90°x-13C) interleaved by two refocusing pulses (180° on 1H and 13C), was used to transform the para-spin order into hyperpolarized transversal 13C magnetization (Fig. 8). The transversal magnetization generated by this method is short-lived and decays with T2*. The l-PH-INEPT+ (ref. 31) sequence, instead, generates long-lasting longitudinal magnetization by the addition of an extra 90°y-13C pulse to PH-INEPT+. Note that the evolution intervals between the pulses of the sequences (t1 and t2) depend on the hydrogen-hydrogen- and hydrogen-carbon J-couplings of the target molecule.
Quantum mechanical simulations were carried out to optimize t1 and t2 and to determine the theoretical polarization yield. The simulations were performed using the product operator and density matrix formalism in a reduced spin system containing the two para-hydrogens and the target nucleus 13C (J-couplings: JH-H=7.57Hz, JH1-C=7.24Hz JH2-C=−5.62Hz)46. It was assumed that only longitudinal spin order survives the hydrogenation process, and that evolution takes place under the isotropic liquid-state Hamiltonian. The optimal timings with respect to the highest polarization yield were obtained by numerical optimization. Relaxation was neglected and rotation operators were applied to mimic the effect of radio frequency pulses. To assess the effect of erroneous intervals, flip angles and J-couplings, these parameters were varied31,47.
For in vitro experiments, 1ml of H2O was filled into the reactor and placed in the isocentre of the scanner (referred to as position 1) to match and tune the coil and to adjust the frequency and field homogeneity (iterative first-order shim). The 1H frequency was manually set to ~2.8p.p.m. The 13C frequency was set to ~185p.p.m., the chemical shift of 1-13C HEP, using the 13CO-resonance of acetone (referred to as model solution M1, 1.1 atom % natural abundance of carbon-13, 8ml, concentration of ~14M, chemical shift of the 13CO resonance 210p.p.m.).
The 13C flip angle was calibrated manually using free induction decays with varying pulse power and an 8ml sample of ethanol at natural abundance (reference pulse gains for a 1ms, 90° pulse of 53.6W (17.2dB) for 1H and 163.5W (8.2dB) for 13C).
For the imaging experiments, the reactor was placed at a distance of 3.5cm to the isocentre (referred to as position 2). The 1H and 13C flip angles were calibrated using a model solution containing 667mg 1-13C sodium acetate in 2ml deionized H2O (denoted as model solution M2, longitudinal relaxation time T1=(22±1) s (see Supplementary Fig. 6), 99 atom % 13C, MW=83.03g mol−1, c=4M, CAS 23424-28-4, Sigma Aldrich, USA) in a cutoff 10mm nuclear magnetic resonance (NMR) tube that was placed within the reaction chamber. Compared with the flip angles measured at position 1, deviations of 1% for 1H and 18% for 13C were found (reference pulse gains of 54.2W (17.1dB) for 1H and 190.5W (7.1dB) for 13C (Supplementary Fig. 7).
Before HP, the first-order shims and frequencies were adjusted for the reactor and the rat using a PRESS48 localization. Both settings were saved and loaded before HP or imaging was conducted.
The receiver gain was set to 64dB for all 13C-experiments.
After the reactor was filled with the precursor solution, closed and placed in the magnet, the automated HP procedure was started, consisting of the following steps: First, the hydrogenation reaction was initialized by injecting pH2 at 15bar (unless indicated otherwise) for a period of 2s, followed by a variable delay of 1–12s, yielding a total hydrogenation time of th=3–14s. Next, the SOT-sequence was executed (~100ms). If the PH-INEPT+ sequence was used, the 13C signal was detected directly at the end of t2; if l-PH-INEPT+ was applied, the magnetization was read out after another delay td, either by non-localized spectroscopy or imaging. Note that ~300μl of the solution was flushed into the outlet tube during the hydrogenation.
After an l-PH-INEPT+ experiment, the T1 of HEP in D2O and H2O was measured by probing the decaying longitudinal magnetization with small-angle acquisitions of 9°, interleaved by 15s (D2O) or 5s (H2O). T1 was extracted from an exponential decay function S(t)=S0·exp(−t/T1)·cos(α)n−1, where S(t) is the acquired signal, S0 is the signal at t=0, α the flip angle (9°) and n the number of the pulse of the series. The absolute polarization of this scan was estimated using the signal of the first acquisition and α. Note, that the data points in Fig. 5 were corrected for polarization loss induced by the previous excitations by dividing the measured signals by cos(α)n−1.
The absolute polarization yield P was quantified with respect to the signal of a thermally polarized sample (M1) for the in vitro experiments, and a model solution containing 333mg 1-13C sodium acetate dissolved in 1.2ml deionized H2O (denoted as model solution M3, concentration of sodium acetate of c=3.3M) for the ex vivo experiments:
where HP and ref indicate a value of the hyperpolarized sample and the reference model solution, N is the number of summated scans (1 for all HP experiments), F13C is the atomic fraction of the 13C isotope, c is the concentration of the molecule, V is the volume of the sample, S the measured 13C-NMR signal and α the excitation flip angle, Ptherm is the thermal 13C-polarization at 7T and room temperature (~6p.p.m.). Note that 100% pH2 enrichment and complete hydrogenation was assumed, which results in an underestimation of the HP that was actually achieved.
The NMR signals were numerically integrated after multiplication with an exponential function (10Hz), Fourier-transformation and automated phase and baseline correction (Topspin 2.0, Bruker, Germany).
The quantification of the hydrogenation yield by NMR of the samples after HP is problematic because the hydrogenation reaction continues after HP. Indeed, complete conversion was found in all samples investigated. Attempts to monitor the conversion during the reaction failed because of low signal (localized spectroscopy, PRESS at 9.4T and~100mM substrate concentration) or strong distortions of the resonances (non-localized spectroscopy).
Instead, the HP yield (P) was recorded as a function of the hydrogenation time th at otherwise identical conditions. From the resulting data, an apparent para-order relaxation time Tpara and a hydrogenation constant Tcat were obtained: we hypothesize that P is governed by a saturated growth described by Tcat and a mono-exponential decay of the para-order (Tpara) after the hydrogenation occurred. By solving the differential equations describing the chemical kinetics, an analytical expression for P(th) was derived and fitted to the experimental data. The function P(th) reads:
The coefficients b and t0 allow the maximum polarization level to be adjusted and a time delay between the application of pH2 pressure and the onset of the hydrogenation reaction, respectively.
An ex vivo rat (rattus rattus, 35g, 7cm, 7 days old) and model solution M3 were placed next to the reaction chamber. An injection hose (42cm, 1/16'', PTFE, SCP GmbH, Germany) was connected to the outlet of the reactor and inserted into the thorax of the rat. The setup was positioned in the coil within the MRI system. The reactor was at a distance of 3.5cm from the isocentre (position 2). The field homogeneity was optimized for two volumes, the position of the reactor and the entire rat. The settings were saved and loaded when needed. After the HP, pH2 pressure was released, and a manual valve (V in Fig. 7) was actuated to inject the HP-tracer directly into the rat without leaving the magnet.
Two-dimensional single-shot RARE (rapid acquisition with relaxation enhancement)49 images were acquired before, as well as~10s and ~41s after the HP was generated (90/180°, RARE factor 38, partial Fourier factor 1.7778, 38·96 matrix, FOV (8.4cm)2, zero-filled to 128·128, (0.65mm)2 in-plane resolution, 6-cm-slice thickness, acquisition time/TR=0.487s, TE=79ms, acquisition time 487ms, bandwidth 10kHz, centred in the isocentre).
Subsequently, a T2-weighted, two-dimensional, 1H-Turbo-RARE sequence was acquired with the same in-plane FOV for anatomical reference (90/180°, RARE factor 8, bandwidth 46.9kHz, matrix 2562, in-plane resolution (328μm)2, TR=2.5s, TE=33ms, acquisition time 80s, 15 slices 1mm thick, 1.5mm apart, centred in the isocenter).
A ZTE MRI was acquired to display the reaction chamber and rat simultaneously (2.3°, matrix 1283, FOV 16.8cm, TR=4ms, acquisition time 208s, bandwidth 300kHz, 51,896 projections, centred in the isocentre).
The SNR was calculated by dividing the maximum signal intensity of a chosen ROI by the standard deviation of the noise (paravision 5.1, Bruker, Germany) (Supplementary Fig. 2 and Supplementary Table 1). For the co-registration, black was set transparent in the 13C image (Fig. 7) (GNU image manipulation program). The ZTE data are shown as a max. intensity projection (imageJ50). The images were composed with Inkscape.
The authors declare that all relevant data presented here are available from the corresponding author upon reasonable request.
How to cite this article: Schmidt, A. B. et al. Liquid-state carbon-13 hyperpolarization generated in an MRI system for fast imaging. Nat. Commun. 8, 14535 doi: 10.1038/ncomms14535 (2017).
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Supplementary Figures, Supplementary Tables, Supplementary Note and Supplementary Reference.
The video shows the injection of parahydrogen (pH2) into the reaction chamber at a pressure of 15 bar, and temperature of ~ 20°C. The video was recorded at 240 frames per second corresponding to a slow-motion factor of 10. The reactor was filled with 1 mL of H2O.
Funding support by the DFG (HO 4604/1-1 and HO 4604/2-1), the German Consortium for Translational Cancer Research, the European Union's Horizon 2020 research and innovation programme under the Marie Sklodowska-Curie grant agreement No 642773 and the contribution of the COST Action TD1103 is gratefully acknowledged.
The authors declare no competing financial interests.
Author contributions A.B.S. and S.B. have contributed equally and have performed the experiments. A.B.S., S.B. and T.L. have implemented the method. J.-B.H., T.L., N.S., C.M., A.D., P.R., S.K. and J.G.S. helped with measurements. A.B.S., T.L. and W.S. designed the reactor. W.S. constructed the reactor. The experiment was devised by J.-B.H. J.H., D.v.E. and J.-B.H. supervised the project and provided the equipment. A.B.S., J.-B.H. and S.B. evaluated and illustrated the results. All authors contributed to the discussion and interpretation of the results. A.B.S. and J.-B.H. wrote the manuscript.