Accelerated stem cell labeling with ferucarbotran and protamine
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- Golovko, D.M., Henning, T., Bauer, J.S. et al. Eur Radiol (2010) 20: 640. doi:10.1007/s00330-009-1585-1
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To develop and characterize a clinically applicable, fast and efficient method for stem cell labeling with ferucarbotran and protamine for depiction with clinical MRI.
The hydrodynamic diameter, zeta potential and relaxivities of ferucarbotran and varying concentrations of protamine were measured. Once the optimized ratio was found, human mesenchymal stem cells (MSCs) were labeled at varying incubation times (1–24 h). Viability was assessed via Trypan blue exclusion testing. 150,000 labeled cells in Ficoll solution were imaged with T1-, T2- and T2*-weighted sequences at 3 T, and relaxation rates were calculated.
Varying the concentrations of protamine allows for easy modification of the physicochemical properties. Simple incubation with ferucarbotran alone resulted in efficient labeling after 24 h of incubation while assisted labeling with protamine resulted in similar results after only 1 h. Cell viability remained unaffected. R2 and R2* relaxation rates were drastically increased. Electron microscopy confirmed intracellular iron oxide uptake in lysosomes. Relaxation times correlated with results from ICP-AES.
Our results show internalization of ferucarbotran can be accelerated in MSCs with protamine, an approved heparin antagonist and potentially clinically applicable uptake-enhancing agent.
KeywordsCell labelingProtamineMesenchymal stem cellFerucarbotranContrast agent
Cell replacement therapy is a promising therapeutic approach for diseases such as type 1 diabetes mellitus , Parkinson’s disease  or myocardial infarction (MI) . Stem cells play an important role as a source of cells destined for implantation. Mesenchymal stem cells (MSCs) are non-hematopoietic stem cells derived from bone marrow and have the distinct advantages of being well characterized, easily obtained and efficiently expanded in vitro compared with other stem cell populations . Patients who received autologous MSCs after an acute MI showed favorable left ventricular remodeling and better ejection fractions than patients who received a placebo . Unfortunately, detecting what happens to engrafted cells after transplantation remains difficult. Magnetic resonance (MR) imaging can provide a non-invasive, real-time diagnostic method for tracking implanted cells .
In order to detect implanted cells via MR imaging, they must be labeled with a contrast agent. Most labeling studies have been conducted using superparamagnetic iron oxide particles (SPIO) or ultrasmall SPIOs (USPIO), which function by creating local field inhomogeneities that cause decreased signal on T2- and T2*-weighted images . Iron oxide-based contrast agents show high MR sensitivity and good biocompatibility . Cell labeling can be achieved by simple incubation with contrast agents [9–11]. Enhanced uptake can be achieved by linking SPIOs to HIV Tat peptides  or by using poly-l-lysine (PLL) , lipofectamine  or dendrimers . While cellular uptake using these agents is greatly increased, these agents are unfortunately not approved by health authorities.
Protamine is a low molecular weight polycationic peptide that is approved as an antidote for heparin anticoagulation . It is also used as a transfection agent for DNA  and oligonucleotides . Arbab et al. have shown that protamine can aid in the uptake of ferumoxides for the application of cell labeling . Ferucarbotran (Resovist) is a SPIO with a carboxydextran coating, a net negative charge and a hydrodynamic diameter slightly smaller than ferumoxides. It is currently in clinical use in Europe for MR examination of focal liver lesions and possesses advantages compared with other iron-based contrast agents, such as its ability to be administered in a bolus. It has been shown that the cellular uptake in monocytes of ferucarbotran is greater and its induction of apoptosis is lower when compared with ferumoxides . Thus, it seems that the combination of protamine and ferucarbotran is promising in order to develop a clinically applicable, fast and efficient method for stem cell labeling for subsequent depiction with MRI.
Materials and methods
Ferucarbotran (Resovist, Bayer Schering Pharma AG, Berlin, Germany) are SPIO particles that are coated with carboxydextran . It has been approved for the MR characterization of focal liver lesions in Europe since 2001. The contrast agent has an r1 relaxivity of 8.7 (8.2–9.2) mM−1s−1, r2 relaxivity of 61 (54–68) mM−1s−1 (at 37°C and 1.5 T in water) and an overall hydrodynamic diameter of 62 nm [19, 20]. The carboxydextran coating ensures optimal dispersion of the nanoparticles within aqueous solutions and bestows upon the complex a net negative charge. Contrast agent was provided as a 1.4-ml ready-to-inject syringe of 0.5 M iron.
Protamine is a group of small (molecular weight 4000–4250) cationic peptides with a high arginine content . It occurs naturally in sperm where it assists in forming a compact structure by binding DNA. Clinically, it is used as an antidote to heparin–induced anticoagulation and as a complexing agent where it prolongs the duration of action of insulin (in the form of NPH insulin). Protamine sulphate stock solution of 50 mg in 5 ml saline solution (0.9%) was obtained (American Pharmaceutical Partners Inc., Schaumberg, IL).
Complex formation between ferucarbotran and protamine was performed by mixing constant concentrations of ferucarbotran (iron concentration of 50 μg/ml) and various concentrations of protamine (0, 1, 3, 5, 7, 10 μg/ml). Respective substances were added directly to the labeling media [Dulbecco’s Modified Eagle Medium (DMEM) + 25% fetal calf serum (FCS)], vigorously shaken and left for 10 min, after which the complexes were utilized for further experiments.
Measurement of size, zeta potential and relaxivity of the contrast agent protamine complexes was performed. The hydrodynamic diameter of the complexes was determined by dynamic light scattering with a Zetasizer 3000 HAS (Malvern Instruments, Herrenberg, Germany). The measurement was performed in labeling media (DMEM + 25% FCS) in order to correctly measure the effective hydrodynamic diameter as would be pertinent to a cell. Five individual measurements were performed on each sample.
The surface charge of the complexes was determined by measuring the electrophoretic mobility in a microelectrophoresis flow cell using a Zetasizer 3000 HAS. To negate the effect of charged particles in the labeling solution, preparation and measurement of the complexes were performed in distilled water. Zeta potentials were measured at least ten times on each sample.
A 1.5-T clinical system (Philips Achieva, Philips Healthcare, Best, The Netherlands) was used for measuring the relaxivity of ferucarbotran/protamine complexes in labeling media. Samples with 1.5 ml of the complex were imaged in Eppendorf tubes placed inside a wrist coil (Medical Advances Inc, Milwaukee, WI). For the simultaneous measurement of T1 and T2, the standard Philips MIX sequence was used. This sequence is an inversion recovery (IR) sequence interleaved with a spin echo (SE) sequence. A 180°–90° pulse pair, separated by the inversion delay TI of 100 ms, is followed by a 90° SE excitation pulse after the SE repetition time TRSE of 650 ms. These three pulses are continuously repeated after the IR repetition time TRIR of 1,500 ms. After every 90° excitation pulse, 20 180° refocusing pulses generate 20 spin echoes (TE 7 ms). The echo trains determine T2, while the ratios of IR to SE signals determine T1 as described in . A 3D sequence with five slices was used to minimize artifacts caused by the otherwise systematically smaller flip angles at the edges of the 2D slices. Only the central three slices were used for parameter quantification. T2* was calculated from the FID of a 2D multi GE sequence using 37 gradient echoes spaced 2.06 ms apart with the first echo situated at 6 ms, TR 1,000 ms and alpha 90°. T2* was determined from the FID assuming a mono-exponential decay of the signal. To obtain relaxivities, the relaxation rates (1/Tx) were plotted against the concentration of iron in the complex using a linear least-square fit.
Cell culture and cell labeling
Mesenchymal stem cell culture was initiated by bone marrow aspirates from a 20-year-old male patient without bone marrow disorder who was admitted to our institution for trauma surgery. The patient gave consent to donating bone marrow via needle aspiration from the posterior iliac crest during surgery. The study was approved by the Institutional Review Board. Preparation of MSCs was done as described in  and cultured using DMEM media (Invitrogen, Carlsbad, CA) supplemented with 10% FCS (HyClone, Logan, UT) and 1% penicillin/streptomycin (Mediatech, Manassas, VA) under standard cell culture conditions (37°C, 5% CO2). MSCs were plated at 80% confluency and let to adhere for one day. Labeling was performed using either 50 μg iron per ml ferucarbotran in DMEM or 50 μg iron per ml ferucarbotran + 5 μg/ml protamine in DMEM + 25% FCS. To investigate whether the addition of FCS might result in efficient uptake, labeling was also performed with 50 μg iron per ml ferucarbotran in DMEM + 25% FCS. Flasks were incubated under standard cell culture conditions for 1, 2, 6, 10 or 24 h. Cells were then washed three times by sedimentation (25°C, 400 ×g, 5 min) with phosphate buffered saline (PBS, Invitrogen) and counted in a Neubauer counting chamber. Trypan blue exclusion testing was performed. Cell counts of 150,000 were resuspended in 400 μl Ficoll solution and transferred into 2.0 ml cylindrical tubes for MR imaging. The isotonic Ficoll solution was prepared with a density of 1.07 g/ml and preserved the viability of the labeled cells during imaging .
MR imaging and data analysis
MR images of labeled cells were obtained using a clinical 3-T MR scanner (Signa EXCITE HD 3 T, GE Medical Systems, Milwaukee, WI) and a standard circularly polarized quadrature knee coil (Clinical MR Solutions, Brookfield, WI). T1- and T2-weighted spin echo (SE) sequences were obtained with varying TR (4,000, 1,000, 500, 250 ms) and TE (60, 45, 30, 15 ms). T2*-weighted gradient echo (GE) sequences were obtained with a flip angle of 30°, a TR of 500 ms and varying TE (31.2, 20.8, 15.6, 10.4, 5.2 ms). Images were acquired with a field of view (FOV) of 120 × 120 mm, a matrix of 256 × 196 pixels, a slice thickness of 1 and 5 mm and one acquisition. To avoid susceptibility artifacts from surrounding air, all probes were immersed in water at room temperature. MR images were transferred as DICOM images to a SUN/SPARC workstation (Sun Microsystems, Mountain View, CA) and processed by a self-written IDL program (Interactive Data Language by Research Systems, Boulder, CO). T1 and T2 relaxation times of the cell samples were calculated assuming monoexponential decay and using a non-linear function least-square curve fitting on a pixel-by-pixel basis. T1 relaxation times were calculated using SE images with a fixed TE of 15 ms. T2 relaxation times were calculated using SE images with a fixed TR of 4,000 ms and variable TE values of 60, 45, 30 and 15. T2* relaxation times were calculated using GE images with a fixed TR of 500 ms and variable TE values of 31.2, 20.8, 15.6, 10.4 and 5.2 ms. The signal intensity for each pixel as a function of time was expressed as follows: SIpixel xy (t) = So (pixel xy) [1-exp(-t/T1pixel xy)] for T1 and SIpixel xy (t) = So (pixel xy) exp(-t/T2pixel xy) for T2 and T2*. T1, T2 and T2* relaxation times of cell samples were derived by ROI measurements on the resultant T1, T2 and T2* maps. Care was taken to analyze only data points with signal intensities significantly above the noise level. Relaxation rates (1/Tx) were derived, and the means and standard deviations of triplicate samples were calculated.
The iron concentrations of all test samples were determined by inductively coupled plasma atomic emission spectrometry (ICP-AES) (IRIS Advantage, Thermo Jarrell-Ash, MA). Samples were dissolved in the microwave (400 W for 55 min) by adding 65% HNO3 and 30% H2O2. The solutions obtained were nebulized into an argon plasma. Collaborators from Bayer Schering Pharma AG Berlin who were blinded with respect to the content of the samples performed these analyses. Means and standard deviations of triplicate samples were derived.
Cells were treated as described and then fixed with 2.5% glutaraldehyde-cacodylate buffer overnight for electron microscopy as described in . In brief, cells were post-fixed in 1% OsO4 and embedded in Epon resin. Thin sections were cut and examined with an EM 10 electron microscope (Carl Zeiss, Oberkochen, Germany). One investigator (A.M.) evaluated the cells for any structural changes as a result of the labeling process as well as the localization of the contrast agent inside the cell.
Contrast agent physicochemical properties
Cell labeling and MR imaging
Qualitative T2-weighted images show pronounced contrast effects in cells labeled with ferucarbotran and protamine at all incubation times investigated (Fig. 3). Quantitatively, all relaxation rates were markedly increased compared with MSCs labeled without protamine. MSCs incubated for 2 h and longer showed R2* rates higher than the corresponding lowest TE (5.2 ms or 0.19 ms−1) used for imaging (Fig. 4). One hour of incubation with protamine resulted in R2 and R2* rates comparable with simple incubation over 24 h. R1 relaxation rates were highest after 6 h of incubation with lower R1 rates seen after 10 and 24 h of incubation.
Cell viability was >90% for all cell labeling protocols with no noteworthy differences found among the different labeling methods and incubation times.
We have shown that the combination of ferucarbotran and protamine is a fast, efficient and potentially clinically applicable method for labeling MSCs for MR imaging. Protamine has been previously used to improve transfection of oligonucleotides , DNA  and cellular uptake of ferumoxides . Being a small protein with a net positive charge, protamine is complexed to negatively charged particles by electrostatic interaction . In the application of DNA transfection, the protein enhances cellular uptake and inhibits nuclease digestion by condensing DNA . In the application of improving cellular contrast agent uptake, results obtained with ferumoxides and protamine show increasing labeling efficiencies with protamine [17, 28, 29]. To our knowledge, this is the first time that cell labeling with ferucarbotran and protamine is reported.
Cell uptake mechanisms for ferucarbotran have not been studied in detail. Ferumoxide, a slightly larger SPIO with a neutral charge, is internalized primarily through scavenger receptor-mediated endocytosis . Scavenger receptors are known to play a role in LDL uptake in macrophages; however, they can internalize structurally unrelated substances such as fibrillar amyloid-β, anionic polysaccharides or bacteria . The cell uptake process involves clathrin, a protein that forms basket-like scaffolds around invaginations caused by receptor ligand complexes on the cell membrane [32, 33]. Although ferumoxides are neutral and ferucarbotran negatively charged, scavenger receptors encompass a number of subtypes with different properties; thus, this explanation may hold for ferucarbotran as well.
The primary problem we experienced when using protamine in combination with ferucarbotran in standard labeling solution not supplemented with 25% FCS was the formation of large aggregates within minutes. The size of the aggregates made them visible to the naked eye, and as such rendered them unsuitable for cell labeling. Similar behavior was noticed when protamine was used to complex oligonucleotides, and it was found that the addition of albumin hindered aggregation [34, 35]. When we attempted to add albumin at different concentrations to a ferucarbotran and protamine solution, no beneficial effect was noticed. However, the addition of FCS at different concentrations slowed (10%) or entirely inhibited (25%) aggregation as demonstrated by serial measurement of hydrodynamic diameter over the course of 24 h. We postulate that components of FCS other than or in addition to albumin coat the ferucarbotran protamine complexes and prevent aggregation.
The physicochemical properties of the ferucarbotran protamine complex are interesting, as particles of different sizes, surface charges and relaxivities can be created by simply varying the concentration of protamine. The MSCs we labeled were responsive to labeling with ferucarbotran and protamine at a concentration at 5 μg/ml. However, other cell lines may not be and may be more responsive to a larger or smaller particle size. While we found it difficult to create stable ferucarbotran protamine complexes with a larger hydrodynamic diameter than approximately 1,100 nm (corresponding to a protamine concentration of 10 μg/ml), the spectrum of hydrodynamic diameters from approximately 100 to 1,100 nm was easily controlled with different protamine concentrations. This may prove beneficial for cell labeling.
Protamine has been used clinically for over 30 years as an antidote for heparin anticoagulation and for slow-release formulations of insulin. One well-known complication is allergoid reactions up to anaphylactic shock . The incidence is fairly low for patients using NPH insulin (0.13%) , but might increase with preconditioning to protamine, such as in a patient undergoing cardiovascular surgery after years of NPH insulin use . If this becomes a problem for our application, low molecular weight protamine fragments — protamine that is enzymatically digested into smaller proteins — may be a solution, as these fragments seem to display lower immunogenicity while retaining most of the beneficial properties of protamine . However, given protamine’s long safety record and seeing that concerns of anaphylaxis may not even be applicable in our setting as protamine is located inside the cell and is invisible to the patient’s immune system, we believe protamine is safe for use in enhancing contrast agent uptake.
Cell labeling can be achieved through a number of means. Cells can be labeled using simple incubation with contrast agent alone, an uptake-enhancing agent can be added, or other means such as electroporation can be utilized. Simple incubation has been used extensively for cell labeling with adequate results for some cell types . In our case, after 24 h of incubation, we noticed contrast agent uptake that resulted in detection on qualitative imaging; however, even better results were obtained with much lower incubation times when protamine was added. Other transfection agents such as lipofectin or poly-L-lysine (PLL) can be used to expedite labeling with great success [39, 40]. However, unlike protamine, most uptake-enhancing agents are not approved by health authorities and as such will have limited usefulness for cell tracking applications in humans. Other techniques such as electroporation circumvent this problem by avoiding uptake-enhancing agents altogether [41, 42]. This method can offer almost instant labeling, but results in significantly lower cell viability after the labeling process. A method utilizing protamine with near-instant labeling but without deleterious effects on viability is preferred.
We acknowledge various limitations of our study. In particular, although such a technique is promising for in vivo cell tracking purposes, results must be validated in further preclinical testing. We realize that our enhanced labeling method relies on fetal calf serum (FCS) in order to stabilize the complexes and to culture the MSCs. FCS is not approved for human use, and as such, the tolerance and clinical applicability are unknown. Also, potential detrimental effects on long-term cell survival or differentiation capacity should be assessed.
In conclusion, we have shown that the addition of protamine greatly improves cellular labeling of MSCs with ferucarbotran. Given the high sensitivity of iron oxide-based contrast agents and the straightforward labeling method with the health authority-approved protamine, future use of this technique to label stem cells destined for cellular and molecular imaging is promising.
We would like to thank Mrs. Gabriele Terfloth for her technical assistance with EM imaging. Additionally, we would like to thank Dr. Christian Plank and Mrs. Olga Mykhaylyk for their assistance with the DLS equipment. This work was supported by a seed grant from the Department of Radiology, University of California of San Francisco, and a grant from the National Institute of Arthritis and Musculoskeletal and Skin Diseases (grant no. NIH R01AR054458).
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