Open Access

Regional contrast agent quantification in a mouse model of myocardial infarction using 3D cardiac T1mapping

  • Bram F Coolen1,
  • Tessa Geelen1,
  • Leonie EM Paulis1,
  • Klaas Nicolay1 and
  • Gustav J Strijkers1Email author
Journal of Cardiovascular Magnetic Resonance201113:56

DOI: 10.1186/1532-429X-13-56

Received: 17 May 2011

Accepted: 5 October 2011

Published: 5 October 2011



Quantitative relaxation time measurements by cardiovascular magnetic resonance (CMR) are of paramount importance in contrast-enhanced studies of experimental myocardial infarction. First, compared to qualitative measurements based on signal intensity changes, they are less sensitive to specific parameter choices, thereby allowing for better comparison between different studies or during longitudinal studies. Secondly, T1 measurements may allow for quantification of local contrast agent concentrations. In this study, a recently developed 3D T1 mapping technique was applied in a mouse model of myocardial infarction to measure differences in myocardial T1 before and after injection of a liposomal contrast agent. This was then used to assess the concentration of accumulated contrast agent.

Materials and methods

Myocardial ischemia/reperfusion injury was induced in 8 mice by transient ligation of the LAD coronary artery. Baseline quantitative T1 maps were made at day 1 after surgery, followed by injection of a Gd-based liposomal contrast agent. Five mice served as control group, which followed the same protocol without initial surgery. Twenty-four hours post-injection, a second T1 measurement was performed. Local ΔR1 values were compared with regional wall thickening determined by functional cine CMR and correlated to ex vivo Gd concentrations determined by ICP-MS.


Compared to control values, pre-contrast T1 of infarcted myocardium was slightly elevated, whereas T1 of remote myocardium did not significantly differ. Twenty-four hours post-contrast injection, high ΔR1 values were found in regions with low wall thickening values. However, compared to remote tissue (wall thickening > 45%), ΔR1 was only significantly higher in severe infarcted tissue (wall thickening < 15%). A substantial correlation (r = 0.81) was found between CMR-based ΔR1 values and Gd concentrations from ex vivo ICP-MS measurements. Furthermore, regression analysis revealed that the effective relaxivity of the liposomal contrast agent was only about half the value determined in vitro.


3D cardiac T1 mapping by CMR can be used to monitor the accumulation of contrast agents in contrast-enhanced studies of murine myocardial infarction. The contrast agent relaxivity was decreased under in vivo conditions compared to in vitro measurements, which needs consideration when quantifying local contrast agent concentrations.


Mouse models of myocardial infarction are widely used to investigate the cascade of events occurring after myocardial ischemia/reperfusion injury. Cardiovascular magnetic resonance (CMR) has proven to be the modality of choice for such studies, as it can produce high-resolution information on both global and local indices of cardiac pathology [13]. Also, MRI contrast agents are increasingly applied as they allow monitoring of various kinds of disease-related processes on cellular and even molecular level, such as cell death, inflammation and fibrosis [46].

For commonly used T1-weighted imaging, the accumulation of paramagnetic contrast agent is associated with local changes in signal intensity. However, signal intensity is an indirect and qualitative measure of concentration, because it is influenced by several other factors, such as coil sensitivities, gain calibration, sequence timing parameters and fluctuations in ECG- or respiratory triggering intervals. Consequently, there is a growing interest for the application of T1 mapping protocols in contrast-enhanced studies of myocardial infarction using T1 contrast agents. Bohl et al. [7] used a Look-Locker T1 mapping method to rapidly measure changes in T1 in both remote and infarct areas after injection of Gd-DTPA. Quantitative knowledge of T1 was translated to the inversion time that resulted in optimal contrast in late Gd enhancement (LGE) imaging. Similar implementations of this method have also been used to dynamically measure T1 after infusion of Mn2+, an ion that acts as a Ca2+ analogue, to report on Ca2+ handling [8, 9].

In this study, we investigated whether quantitative T1 measurements can also serve for the assessment of local contrast agent concentrations. This is particularly valuable for molecular imaging, where one aims to relate local amounts of contrast agent to the presence of certain disease markers. We recently presented a novel imaging protocol for measuring mouse myocardial T1 with whole-heart coverage, based on retrospective triggering and variable flip angle analysis [10]. Good reproducibility of measuring regional T1 was found between measurements at successive days; however, limited data was available concerning changes in T1 in infarcted myocardium upon injection of a Gd-based contrast agent. Here, we hypothesize that this method provides an accurate read-out of regional contrast agent induced changes of myocardial T1 in a mouse model of ischemia/reperfusion injury and allows for determination of local contrast agent concentrations. To test this hypothesis, we measured the accumulation of a liposomal contrast agent after myocardial ischemia/perfusion injury and quantified local changes in T1 using three-dimensional T1 mapping. Then, ΔR1 values derived from pre- and post-contrast in vivo T1 maps were correlated to contrast agent concentrations obtained from ex vivo inductively coupled plasma mass spectrometry (ICP-MS).

The use of a liposomal contrast agent allowed for T1 measurements several hours after contrast agent injection at a time point at which the contrast agent was almost cleared from the blood circulation and did not contaminate the measurement of myocardial T1. In this application, myocardial contrast agent concentrations were stable for an extended period of time, which increased the available imaging time and allowed for full 3D coverage of the heart. Moreover, the use of liposomes in this experimental mouse model of myocardial infarction provided the opportunity to perform relevant validation experiments concerning in vivo quantification of the actual contrast agent concentration and relaxivity properties in the heart.

Materials and methods

Contrast agent preparation and characterization


Paramagnetic liposomes were prepared as described earlier [11]. In short, liposomes were prepared by lipid film hydration of a lipid mixture containing 100 μmol of total lipid. This mixture consisted of gadolinium-diethylenetriaminepentaaceticacid-bis(stearylamide) (Gd-DTPA-BSA, Gateway Chemical Technology, St. Louis, MO, USA), 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC, Lipoid GmbH, Ludwigshafen, Germany), cholesterol (Avanti Polar Lipids, Alabaster, AL, USA), 1,2-distearoyl-sn-glycero-3-phospoethanolamine-N-[methoxy(poly(ethylene glycol))-2000] (PEG2000-DSPE, Lipoid GmbH) and 1,2-distearoyl-sn-glycero-3-phospoethanolamine-N-[maleimide(poly (ethylene glycol))-2000] (Mal-PEG2000-DSPE, Avanti Polar Lipids) at a molar ratio of 0.75/1.1/1/0.075/0.075. The resulting vesicles were sized by extrusion through 200 nm filters (four times), followed by extrusion through two 100 nm filters (ten times). Liposomes were concentrated by centrifugation at 55000 rpm and 4°C for 1 hour. Finally, liposomes were resuspended in HEPES-buffered saline (20 mM HEPES and 135 mM NaCl, pH 7.4) at a concentration of approximately 70 mM of total lipid.


The final total lipid concentration was determined with a phosphate analysis according to Rouser [12]. Dynamic light scattering (DLS) was performed at 23°C with a Malvern ZetaSizer Nano S and the resulting hydrodynamic diameter of the liposomes was approximately 115 nm. Longitudinal relaxivity r1 at 9.4T was measured in HEPES-buffered saline at 37°C. For this purpose, T1 measurements were performed on samples with various concentrations of Gd-DTPA-BSA (0.01-1.25 mM) using a snapshot-FLASH T1 mapping method [13]. The following parameters were used: scan repetition time = 15 s, TR/TE = 4.0/2.0 ms, α = 15°, Nsegments = 32, slice thickness = 1 mm. A total of 60 inversion times were sampled ranging from 72 to 4792 ms.

In vivomeasurements

Mice were obtained from a commercial breeder (Charles River, Paris, France) and housed under controlled conditions. A total of 13 Swiss mice (male, 33 ± 2 g) were used in this study. In the infarct group (N = 8), mice underwent ischemia/reperfusion surgery by a 30-minute ligation of the left anterior descending (LAD) coronary artery. One day after surgery, CMR was performed, consisting of 3D T1 mapping measurements to assess baseline T1, as well as 3D CINE measurements for determination of wall- thickening. This was followed immediately by injection of a liposomal contrast agent through the tail vein (0.05 mmol Gd/kg). Five control mice served as control group, in which the same CMR measurements and contrast agent administration were performed without previous surgery. Twenty-four hours post-injection, a second T1 measurement was performed using the same protocols. The mice were then sacrificed and the heart was excised to measure the Gd content ex vivo. The study protocols were approved by the local animal ethical committee.

CMR was performed with a 9.4 T Bruker experimental scanner using a 72-mm-diameter volume transmit coil in combination with a mouse cardiac phased-array surface coil (Bruker BioSpin GmbH, Ettlingen, Germany). The latter consists of a 2 by 2 array of square coil elements, each sized 16 × 16 mm2. 3D T1 mapping was performed as published previously [10] using retrospective triggering (3D IntraGate) with variable flip angles. In the current study, three different flip angles α were used (α = 2°, 8° and 14°). This was shown to produce highly reproducible myocardial T1 maps, in which the 95% confidence interval for ΔR1 at baseline values was only 0.15 s-1. After pre-contrast T1 measurements, the same sequence was performed in black-blood mode and α = 8° for assessing wall thickening values. For this particular purpose, black-blood was chosen over bright-blood scans, because of superior wall delineation. On the other hand, black-blood scans are less suitable for T1 mapping (see Discussion). Although the use of retrospective triggering enables reconstruction of an arbitrary number of cardiac frames, a sufficient number averages is needed for each frame. With an imaging time of 20 minutes, reconstruction of 12 cardiac frames provided good quality black-blood 3D CINE images for determining wall thickening values from end-diastolic and end-systolic frames. The total imaging time for each animal was approximately 90 minutes.

Data analysis

Pre- and post-contrast myocardial 3D T1 maps were segmented according to the AHA 17-segment model [14] using a custom-built segmentation algorithm (Mathematica 7.0, Wolfram Research, Champaign, IL, USA). Segmentation was based on the high flip angle T1-weighted scan, in which blood-myocardium contrast was highest. For each segment, mean pre- and post-contrast R1 values were calculated (R1 = 1/T1), as well as corresponding ΔR1 values (R1post - R1pre). Additionally, wall thickness (WT) of all segments was determined from the black-blood 3D IntraGate scans in both end-diastolic (ED) and end-systolic (ES) cardiac phases. Systolic wall thickening (SWT) values were defined as (WTES/WTED - 1) * 100%.

Ex vivoGd quantification

After post-contrast CMR measurements, mice were sacrificed through cervical dislocation. From all mice in the infarct group, the heart was excised and stored in the freezer at -80°C until further use. A mid ventricular slice containing the infarct area (2.5 mm above the apex) was then cut from the heart using a mouse heart slicer (Zivic Instruments, Pittsburgh, PA, USA). The slice was subsequently cut into four segments (septal, posterior, lateral and anterior), each of which was weighed and put in a vial. For all segments, the Gd content (in nanograms) was determined with ICP-MS. The Gd concentration ([Gd]) was then calculated in each segment using the specific gravity of myocardial tissue (1.05 g/ml) and the molar weight of Gd (157.25 g/mol).


Statistical analysis was done with SPSS 17.0 (SPPS, Inc., Chicago, IL, USA) and JMP 9.0 (SAS Institute, Cary, NC, USA). All values are reported as mean ± standard deviation. All tests were performed on the R1 values, rather than on T1 values. The level of statistical significance was set at p = 0.05 for all tests. Pre- and post-contrast R1, as well as ΔR1 values were considered separately. For these parameters, significant differences between infarct, remote and control areas were tested with a one-way ANOVA and post-hoc Tukey test. Note that infarct segments were defined as those segments with a corresponding wall thickening value smaller than 15%, whereas for remote regions, the lower threshold was set at 45%. Differences in ΔR1 as function of wall thickening were also tested using a one-way ANOVA and post-hoc Tukey test. To correlate regional ΔR1 values as estimated from in vivo CMR data with the Gd concentrations as measured by ex vivo ICP-MS, orthogonal regression was performed. This was preferred over linear regression, because errors in both measurement techniques should be taken into account.


Figure 1 shows end-diastolic black-blood images of a representative mouse of the infarct group in four different slices reconstructed from the 3D imaging volume. The entire CINE series containing all cardiac frames is provided as a supplemental movie in Additional File 1. Blood suppression was excellent throughout the whole 3D volume, resulting in good delineation of the cardiac wall without presence of blood flow artifacts. Typically, akinetic regions were found in the postero- and anterolateral wall.
Figure 1

3D black-blood retrospectively triggered CINE images used for determination of wall thickening. 3D black-blood retrospectively triggered CINE images used for determination of wall thickening. Images from left to right represent different slices through the heart towards the apex (movie provided in Additional File 1).

Representative maps from pre- and post-contrast myocardial T1, as well as corresponding post-contrast T1-weighted images are shown in Figure 2. Akinetic regions apparent from Figure 1 can already be distinguished in the pre-contrast T1 maps (Figure 2A) from an increase in T1. However, they are more evident in the post-contrast images from a large increase in signal intensity (Figure 2C, arrows) and corresponding significant decrease in T1 (Figure 2B).
Figure 2

Pre-contrast myocardial T 1 (A), post-contrast myocardial T 1 (B), and post-contrast T 1 -weighted images (C) in a mouse with myocardial infarction. Pre-contrast myocardial T1 (A), post-contrast myocardial T1 (B), and post-contrast T1-weighted images (C) in a mouse with myocardial infarction. Arrows mark infarct regions showing contrast enhancement in post-contrast T1-weighted imaging. Images represent the same slices as in Figure 1.

Figure 3A shows Bull's eye plots of regional values of ΔR1 (R1post - R1pre) and wall thickening of the same mouse as in Figure 2. The latter was divided into three categories, where SWT values < 15% and > 45% were considered 'infarcted' or 'remote', respectively [1, 15]. Regions of low SWT matched with regions of high ΔR1 values, induced by the presence of the paramagnetic liposomes. The mean ΔR1 as function of SWT is plotted in Figure 3B. ΔR1 decreased rapidly with increasing percentage of wall thickening, but only severely infarcted regions revealed significantly elevated ΔR1 values compared to remote regions. For comparison, SWT in healthy control mice was 65.0 ± 12.3%.
Figure 3

Relation between wall thickening and contrast agent accumulation. (A) Bull's eye plots of ΔR1 and wall thickening (SWT) values corresponding to the animal in Figure 1. Regions with SWT < 15% are considered infarcted, whereas remote regions have SWT > 45%. (B) Relation between wall thickening and their corresponding ΔR1 values (mean value of all animals, * p < 0.01).

Statistical differences in pre-contrast T1, post-contrast T1 and ΔR1 between infarct, remote and control regions are elaborated in Figure 4. For all parameters, there was a significant difference (p < 0.01) between the infarct regions on the one hand and both control and remote regions on the other hand. In pre-contrast T1 scans, the mean T1 of infarcted myocardium was elevated (2030 ± 131 ms) as compared to remote (1761 ± 114 ms) and control values (1667 ± 50 ms). Post-contrast T1 values were decreased compared to pre-contrast T1 in infarct (910 ± 107 ms), remote (1400 ± 196 ms) as well as control (1203 ± 86 ms) regions. T1 was significantly lowest in the infarcted myocardium. The post- and pre-contrast longitudinal relaxation rate difference (ΔR1) was largest for the infarct region (0.60 ± 0.13 s-1). However, also in remote tissue and in control animals the contrast agent resulted in a significant ΔR1 (0.15 ± 0.08 s-1 and 0.23 ± 0.05 s-1, respectively, not significantly different). Since the liposomal contrast agent does not extravasate from healthy blood vessels, these R1 changes in remote and control tissues are likely caused by contrast agent still circulating in the blood 24 hours post injection.
Figure 4

Statistical analysis. Statistical analysis of pre-contrast T1, post-contrast T1 and ΔR1 for infarcted, remote and control tissue (* p < 0.01).

Figure 5 shows the relation between ΔR1 values determined by in vivo CMR and Gd concentrations determined by ex vivo ICP-MS. When considering all segments that were analyzed separately (Figure 5A), the Pearson correlation coefficient r was 0.6 with R2 = 0.36. However, a more substantial correlation was found after averaging values for each heart slice (r = 0.81) with a corresponding R2 of 0.65 (Figure 5B). Furthermore, a small but significant offset for ΔR1 was found in both analyses. The slope is the effective in vivo relaxivity of the liposomal contrast agent r1 = 1.06 mM-1s-1. This was significantly lower than r1 = 2.2 mM-1s-1 (R2 = 0.99) for the liposomes in suspension in vitro.
Figure 5

Correlation between regional ΔR 1 and Gd concentration . Correlation between regional ΔR1 values determined by in vivo CMR and Gd concentration determined by ex vivo ICP-MS. The analysis was done either on all individual heart segments (A) or after averaging all values in each heart slice (B).


In this paper we described the use of 3D T1 mapping to assess myocardial relaxation rates after ischemia/reperfusion injury before and after administration of a liposomal contrast agent. This type of contrast agent is especially known for its high relaxivity per particle and long circulation half-life [16], but also for its prolonged retention in the infarcted tissue, allowing visualization of the contrast agent many hours after administration [1719].

In this study, we chose to perform post-contrast measurements 24 hours after contrast agent injection. The 24 hours time period allowed for sufficient accumulation of contrast agent in the infarct area, while at the same time providing sufficient clearance of the contrast agent from the blood. Similar ΔR1 values in remote and control tissue however suggested that a small amount of contrast agent was still present in the blood. At later time points, full blood clearance would have been achieved, but probably at the expense of efflux of contrast agent from the infarction. Also, it is known that infarct development and healing is a very dynamic process, whereas pre- and post-contrast measurements are aimed at representing the same infarct status. Therefore we limited our T1 quantification to the 24 hours time period. Previous experiments have shown a negligible mean effect of repeated measurements on R1 [10]. In future experiments, pre- and post-contrast blood T1 measurements could be incorporated to better quantify the influence of blood contrast agent concentration levels on myocardial T1 changes.

The black-blood protocol used in this study for functional measurements could also have been used for myocardial T1 mapping. However, although black-blood imaging was very effective in suppressing signal from the blood (see Figure 1), it does not prevent exchange of blood magnetization with the myocardium and therefore does not eliminate contamination of myocardial signal due to presence of contrast agent in the blood. Also, we have previously shown that saturation of the blood results in dramatically lower effective myocardial T1 values [10].

Based on regional ΔR1 values, a significantly higher uptake of contrast agent was found in infarct regions compared to remote and control regions. The identification of regions being either 'infarcted' or 'remote' was based on wall thickening values determined from functional CINE measurements (Figure 1). We chose rather conservative threshold values for wall thickening (< 15% and > 45%) to ensure proper identification of infarct and remote areas [1, 15]. Additionally, it was shown that the infarct area had a significantly higher T1 value already in pre-contrast scans. Previously, elevated T1 values in infarcted myocardium have been attributed to several different mechanisms. Some studies argue that formation of myocardial edema early after ischemia results in T1 increase due to a larger fraction of free water [7, 20]. The increased wall thickness in the infarcted myocardium visible in end-diastolic images (Figure 1) indeed supports this theory. Others [21] claim that this increase of myocardial T1 is more likely caused by a decrease in perfusion, based on iso-intense remote and infarcted tissue in proton density weighted images. The use of a surface coil in this study creates a signal intensity gradient in our cardiac images, which made it difficult to assess proton density and corroborate or negate the latter hypothesis.

An ongoing topic within in the field of contrast-enhanced MR imaging is the actual quantification of regional contrast agent accumulation. With respect to small animal cardiac imaging, this is one of few studies attempting to correlate contrast agent induced ΔR1 values derived from in vivo CMR measurements with contrast agent concentrations determined by ex vivo analysis [9]. When analyzing all segments (4 in each mouse) separately, only a weak correlation was found. However, a substantial correlation was found when concentration values of all four segments within the slice were averaged. We believe that weak correlation of individual segments is caused by inaccuracies in cutting the heart slices into exactly the same segments as those of the in vivo CMR. Because of the generally sharp demarcations of the infarct, small errors in circumferential division and sectioning of the left ventricle can therefore lead to substantial differences in Gd concentrations. We therefore believe that a significant part of the variation is caused by inaccuracies of the cutting procedure. Reproducibility of regional T1 quantification of healthy myocardium using the current CMR protocol was demonstrated previously [10]. In the present study, we found the same myocardial T1 values for the control group, proving reproducibility of the method across studies. Ex vivo determined Gd concentrations correlated fairly well with in vivo ΔR1 values. Taken together, we therefore conclude that regional quantification of contrast agent concentrations is feasible.

At this point, the mechanism of contrast agent accumulation is believed to be passive accumulation throughout the increased extracellular space by extravasation of the liposomes through leaky vasculature in the reperfused injured myocardium [22]. Regression analysis interestingly showed that the effective relaxivity of the liposomes in vivo was lower compared to that determined in vitro. Reduced relaxivity could be mediated by the cellular environment of the myocardium, partial volume effects or compartmentalization of the liposomes [23]. Compartmentalization may result from phagocytosis of liposomes by macrophages. Whether or not phagocytosis occurs also depends on the liposomal formulation [18, 22]. Future studies could focus on combining regional quantification of contrast agent concentrations with more detailed histological analysis on the cellular level to reveal the exact mechanisms of uptake. Importantly, in vivo relaxivity values must be considered for correct estimation of Gd concentrations from ΔR1 values.


In summary, the quantitative T1 mapping technique described in this study provides a reproducible tool to monitor the accumulation of contrast agents in contrast-enhanced studies of murine myocardial infarction. A particular field of application is that of targeted contrast agents, which are used for mapping the spatial distribution of specific biomarkers. The contrast agent relaxivity was found to be lower than that measured in vitro, which needs consideration when quantifying local contrast agent concentrations.

List of abbreviations


analysis of variance


inductive coupled plasma mass spectrometry


left anterior descending


wall thickness


systolic wall thickening.



The authors want to acknowledge Peter Leenders for performing surgery and Leonie Niesen for biotechnical assistance.

Funding sources

Grant sponsor: Dutch Technology Foundation STW, applied science division of NWO and the Technology Program of the Ministry of Economic Affairs; Grant number: 07952.

Authors’ Affiliations

Biomedical NMR, Department of Biomedical Engineering, Eindhoven University of Technology


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