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A Comparison of the Sensitivity and Cellular Detection Capabilities of Magnetic Particle Imaging and Bioluminescence Imaging

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04 October 2024

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07 October 2024

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Abstract
Preclinical cell tracking is enhanced with a multimodal imaging approach. Bioluminescence imaging (BLI) is a highly sensitive optical modality which relies on engineering cells to constitutively express a luciferase gene. Magnetic particle imaging (MPI) is a newer imaging modality which directly detects superparamagnetic iron oxide (SPIO) particles used to label cells. Here, we compare BLI and MPI for imaging cells in vitro and in vivo. Mouse 4T1 breast carcinoma cells were transduced to express firefly luciferase, labeled with SPIO (ProMag) and imaged as cell samples and after subcutaneous injection into mice. For cell samples, the BLI and MPI signals were strongly correlated with cell number. Both modalities presented limitations for imaging cells in vivo. For BLI, weak signal penetration, signal attenuation and scattering prevented detection of cells for mice with hair and for cells far from the tissue surface. For MPI, background signals obscured the detection of low cell numbers due to the limited dynamic range and cell number could not be accurately quantified from in vivo images. It is important to understand the shortcomings of these imaging modalities to develop strategies to improve cellular detection sensitivity.
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Subject: Biology and Life Sciences  -   Biophysics

1. Introduction

Cellular imaging techniques have been used to track cancer cells, stem cells and immune cells in both preclinical and clinical scenarios. In the context of cancer, cell tracking has been helpful in characterizing tumour growth [1], viability [2] and metastasis [3,4,5,6] and for imaging the homing of circulating tumour cells which have been studied as delivery vehicles for cancer therapeutics [7]. A variety of immune cell types have been tracked. Preclinical and clinical studies have imaged tumour-associated macrophages as a marker of tumour aggressiveness [8,9,10]. Multiple modalities have been used to track natural killer cells [11,12], cytotoxic T cells [13,14] and dendritic cells [15] in tumour-bearing mice. Imaging has captured neutrophil infiltration in wound healing [16], and macrophage homing in models of heart disease [17]. In vivo cell tracking has also been employed to monitor the biodistribution of transplanted stem cells [18,19,20] and for tracking stem cell homing in diseases such as cancer [21] and stroke [22].
Different imaging modalities can be used for cell tracking, each with their own strengths and limitations. The most common modalities include bioluminescence imaging (BLI), positron emission tomography (PET), and magnetic resonance imaging (MRI). Bioluminescence imaging (BLI) is an optical modality which utilizes cells that are genetically engineered to constitutively express a luciferase reporter gene. To generate signal, a luciferin substrate is administered to animals harboring luciferase-expressing cells. Luciferin is catalyzed by the luciferase enzyme, and photons of light are released as a by-product of this reaction. Photons are captured by a cooled charge-coupled device camera and converted into electric signal. BLI is highly specific, as luciferase genes are not endogenously expressed in mammalian cells [23]. It is also highly sensitive, with one group reporting the detection of a single cell in the mouse lung microvasculature [24]. Other major benefits of BLI include the ability to track cell proliferation and viability. There is no label dilution over time, as luciferase is stably expressed through each cell division. Some luciferase enzymes require ATP as a co-factor to drive the enzymatic reaction, hence only live cells produce signal. However, there are limitations with this modality. BLI signal is attenuated through tissue, and this limits the depth of imaging to 1-2 cm. Luciferase genes and substrates with a further red-shifted, or near-infrared shifted, emission wavelength have improved signal intensity at greater tissue depths [25]. This modality also has no potential for clinical translation, as cells must be engineered to express luciferase.
PET is a nuclear imaging modality that can be used to image cells labeled with a radiotracer. PET signal is produced via radioactive decay of the tracer, which causes the emission of a positron. An annihilation event occurs when this positron encounters an electron in tissue. The collision produces two gamma rays which travel in exact opposite directions until they hit the scanner’s detector. PET imaging is highly sensitive, and the quantity of tracer can be measured. For cell tracking, tracers can be incubated with cells in vitro, or tracers can be injected intravenously and taken up by cells in vivo [26]. The short half-life and high cost of production for PET tracers are limitations. Some costs can be saved preclinically by imaging multiple mice at once [27]. The exposure to tracer radiation has also been shown to cause DNA damage to cells, which can affect proliferation and viability [28,29]. PET images provide limited anatomical information and have low spatial resolution. They are often paired with a high-resolution modality, such as MRI [30,31].
Cells directly labeled with superparamagnetic iron oxide (SPIO) particles can be imaged with magnetic resonance imaging (MRI). Unlike PET, MRI does not produce any radiation, and several clinical trials have been conducted using SPIO-based MRI for cell tracking [8,32,33]. SPIOs indirectly produce MRI signal through local magnetic field distortions, which leads to rapid dephasing of surrounding protons. This causes a reduction in signal intensity on a T2-weighted MRI, thus producing a hypointense (dark) region on the image where SPIOs are present [34]. The signal void is larger than the size of a single cell which provides MRI with single cell sensitivity under ideal imaging conditions [35]. However, it is not possible to directly quantify cell number from these signal voids. SPIO-based MRI also has low specificity, as signal voids produced by SPIOs can be hard to distinguish from other anatomical regions that similarly appear dark [34].
Recently, a new imaging modality has emerged with the capability of directly quantifying SPIO-labeled cells. First reported in 2005, magnetic particle imaging (MPI) detects signal directly from SPIOs. The scanner consists of two electromagnets that generate a gradient magnetic field known as the selection field. At the center of the selection field, there exists a field-free region (FFR) where SPIOs experience net zero magnetization. When an alternating magnetic field known as the drive field is applied, SPIOs within the FFR can respond by flipping their magnetic dipole. SPIOs outside of the FFR are magnetically saturated and cannot respond to the drive field. The FFR is moved across the imaging field of view, and the MPI signal is linearly proportional to the amount of SPIOs within this FFR at any given point [36]. This technique is advantageous over MRI cell tracking, as it provides a directly quantifiable, positive contrast or “hotspot” image of SPIO-labeled cells. The slope of a calibration line measuring the MPI signal of known amounts of SPIO can be used to calculate iron mass from an image. Samples with a known cell number can then be used to calculate the amount of iron per cell, and this value can be used to estimate the number of cells in subsequent images [37]. Direct cell quantification is not possible with any other imaging modality. SPIO-labeled cells can be imaged in vivo, and signal is not attenuated through tissue. However, MPI also does not provide any anatomical information, and a secondary imaging modality is required, such as MRI or CT [4,38]. Table 1 compares BLI, PET, SPIO-MRI, and MPI for preclinical cell tracking.
Multimodal imaging strategies which combine two or more modalities have been widely used to take advantage of the strengths of each imaging modality and minimize the drawbacks [1,3,5,39,40]. This has the potential to provide a more complete picture of the fate of a population of cells in vivo. In this study we compare MPI to BLI. We also evaluate the strengths and limitations of each modality for in vivo cell detection and gauge the ways that MPI and BLI can be used in a complementary fashion.

2. Materials and Methods

2.1. Cell Culture

Mouse 4T1 breast carcinoma cells were cultured in Dulbecco’s modified eagle’s medium (DMEM) (Wisent Inc, QC, CAN) supplemented with 10% fetal bovine serum and 5% antimycotic/antibiotic. Cells were passaged every 2-3 days at 80% confluency and maintained at 37 °C and 5% CO2.

2.2. Fluorescence Activated Cell Sorting (FACS)

4T1 cells were transduced to co-express firefly luciferase (fluc) and green fluorescent protein (GFP) using the RediFect Red-FLuc-GFP commercial lentiviral vector (Revvity, MA, USA). Transduced cells were sorted based on the intensity of GFP fluorescence using a FACSAria III cell sorter (BD Biosciences, NJ, USA) with FACSDiva software (Version 9.0.1, Windows 10) at the London Regional Flow Cytometry Facility (University of Western Ontario, ON, CAN). Briefly, cells were suspended in PBS with 2% fetal bovine serum (FBS) at a concentration of 30 x 106 cells/mL. GFP was detected using the blue laser trigon on the B 530/30 channel (blue trigon detector B – 530/30 bandpass and 502 longpass filter). Sorted cells were collected in a buffer consisting of 50% DMEM and 50% FBS. After five days in culture, cell viability was assessed based on sytox blue exclusion. Sytox blue was added to cells at a 1:1000 dilution and was detected on the V 450 / 40 channel (violet trigon detector C – 450 / 40 bandpass filter). A live cell gate (FSC-A vs Violet 450/40) was created to specifically select viable cells. After the sort, GFP fluorescence was qualitatively assessed using an ECHO 4 revolve microscope (CA, USA).

2.3. Characterization of ProMag

The SPIO particle used in these experiments was a magnetic microsphere called ProMag (ProMag 1 Series – COOH, Bangs Laboratories, IN, USA). ProMag consists of polymer encapsulated iron oxide particles where many iron nanocrystals are clustered within a polymer matrix. The diameter of each microsphere is 1 μm. The inert polymer coating limits their degradation [41]. The sensitivity and resolution of ProMag were characterized using the RELAX module on a Momentum preclinical MPI scanner (Magnetic Insight, CA, USA). Particle sensitivity was defined as the peak amplitude of the point spread function (PSF) normalized to iron content (μg). The resolution of ProMag was measured as the full width half maximum (FWHM) of the PSF displaying MPI signal normalized to iron content (μg) and maximum signal (A.U). The FWHM (T) was divided by the gradient field strength used for imaging (3.055 T/m) to determine the resolution in millimeters.
Images of samples of known amounts of ProMag (6.50 μg, 3.25 μg, 1.625 μg, 0.813 μg, and 0.406 μg) were acquired individually by MPI to evaluate the relationship between ProMag concentration and MPI signal. 2D images (1 projection, 2 minutes) were acquired using a 12 cm x 6 cm (z, x) field of view (FOV) with high sensitivity settings (3.055 T/m gradient, 20 (x) and 26 (z) excitation amplitudes). An image of the empty sample bed was also acquired for image quantification. A linear regression was used to plot total MPI signal (A.U) against iron mass (μg) for each sample. The slope of this line was used to quantify iron mass from subsequent images of cell samples.

2.3. Cell Labeling Procedure

Cells were cultured in a T75 cm2 flask supplemented with 10 mL of DMEM. At 80% confluency, cells were labeled with ProMag (25 μg/mL) by introducing 52 μL of ProMag in DMEM (total volume of 10 mL). After a 24-hour incubation period, the cells were washed three times with PBS and trypsinized to detach them from the culture flask. Cells were then diluted in DMEM to deactivate the trypsin and centrifuged at 1000 rpm for 5 minutes. Three additional washing steps were performed in phosphate buffered saline (PBS) (Wisent Inc.) to remove cellular debris and free iron. To isolate labeled cells, magnetic column separation was performed using an EasySep magnet (Stem Cell Technologies, BC, CAN). Cells were placed in a 5 mL flowtube and inserted into the magnet for 5 minutes. Labeled cells were washed from the sides of the tube with PBS.

2.4. Cell Labeling Efficiency – Perls’ Prussian Blue and Magnetic Column Separation

Perls’ Prussian blue (PPB) staining was performed to visualize ProMag within cells. 2 x 105 cells suspended in 300 μL of PBS were placed within a cytofunnel attached to filter paper and a glass slide. The apparatus was placed within a cytospin 4 centrifuge (Thermo Fisher Scientific, CA, USA) and centrifuged at 1000 rpm for 5 minutes. The slide was then fixed in a 3-part methanol, 1-part acetic acid solution for 5 minutes. A PPB solution was created by dissolving 0.5 g of potassium ferrocyanide in 25 mL of ultra-pure water, followed by the addition of 25 mL of 2% hydrochloric acid. After the solution was filtered, the slide was submerged for 30 minutes and iron within the cells was stained blue. Then, the slide was counterstained with a filtered nuclear fast red solution for 5 minutes, resulting in cell nuclei appearing red. The stained cells were then dehydrated by exposing the slide to increasing concentrations of ethanol (70%, 95% and 100%), followed by two xylene washes. Finally, the slide was sealed with cytoseal protectant and a coverslip. PPB slides were visualized using the Echo 4 Revolve Microscope (CA, USA).
To quantify cell labeling efficiency another way, cell counts were performed before (n=3) and after (n=3) magnetic column separation using the trypan blue exclusion assay (Countess Automated Cell Counter, Invitrogen, CA, USA). The labeled cells were prepared following the steps listed above. The % labeling efficiency was quantified by dividing the average cell count after magnetic separation by the average cell count before magnetic separation. This was repeated three separate times, and each time the % labeling efficiency was quantified.

2.5. In Vitro Cell Imaging

2.5.1. BLI as a Measure of Cell Viability

The BLI signal of unlabeled and ProMag-labeled cells was compared in vitro to assess the effects of labeling on cell viability. Six replicates of 51,200, 25,600, 12,800 and 6,400 cells were added to a black 24-well plate and topped with 500 µL of complete DMEM. The cells were left overnight to adhere to the plate. The following day, half of the samples (triplicates of each cell number) were labeled with ProMag (25 µg/mL) for 24 hours. Immediately before BLI, all wells (labeled and unlabeled cells) received 5 µL of D-luciferin (30 mg/mL). BLI images were acquired on an IVIS Lumina XRMS Series 3 In Vivo Imaging System (Revvity). Images were acquired until each sample reached the peak radiance (p/sec/cm2/sr).

2.5.2. Calculating Iron Content Per Cell

To estimate the amount of iron present in each cell, triplicate samples of 500,000 ProMag-labeled cells were suspended in 250 µL of DMEM and imaged with MPI. The same scan parameters were used as previously described for imaging the calibration line samples. The amount of iron calculated for these samples was divided by 500,000 (known number of cells imaged) to calculate iron per cell. The average iron loading per cell was reported as the mean of the three samples imaged.

2.5.2. Comparing the Sensitivity of MPI and BLI In Vitro

To directly compare the in vitro sensitivity and cell detection limits of MPI and BLI, triplicate samples of ProMag-labeled cells were prepared in a 1:2 dilution series consisting of samples ranging from 51,200 to 100 cells (total of 30 samples). All samples were suspended in 250 µL DMEM and imaged on the same day with BLI and MPI. Samples were kept on ice when not imaged to preserve cell viability.
Cell samples were imaged with BLI first. Prior to imaging 2.5 µL of D-luciferin (30 mg/mL) was added to each sample. One batch of images was acquired for triplicate samples of 51,200 cells to 3,200 cells (total of 15 samples, 20 min scan). Then, a second batch of images was acquired for triplicate samples of 1,600 cells to 100 cells (total of 15 samples, 20 min scan). Images were acquired until all samples reached peak radiance.
2D MPI was performed immediately after BLI. Cell samples were imaged individually using the scan parameters described previously. Cell number was calculated by dividing the total iron content (μg) in each image by the average iron per cell. For samples of lower cell numbers that could not be resolved and quantified in 2D, 3D images were acquired (35 projections) with a smaller FOV 3 x 6 cm (z, x) to shorten scan time from 30 minutes to 17 minutes.

2.6. Mice

In vivo, the sensitivity and cell detection limits of MPI and BLI were directly compared using different strains of mice. C57Bl/6 (n=1), Balb/c (n=1) and nu/nu (n=2) mice were obtained from Charles River Laboratories, Inc (Senneville, QC, CAN). All animals were cared for in accordance with the Standards of the Canadian Council on Animal Care and Western University’s Council on Animal Care under an approved animal use protocol. Mice were fasted for 12 hours prior to imaging to minimize background gastrointestinal signal in MPI.

2.6.1. Cell Preparation for Animal Injection

Cells labeled with ProMag (25 µg/mL) were suspended in 25 µL of PBS and stored on ice prior to each injection. Immediately before injection, each sample was mixed with 25 µL of Matrigel (50 µg/mL) for a combined injection volume of 50 µL. To characterize in vivo detection limits of MPI and BLI, one nu/nu mouse was injected with 6,400 labeled cells subcutaneously at the back of the neck. Three other mice (C57Bl/6 (n=1), Balb/c (n=1) and nu/nu (n=1)) were injected with 12,800 labeled cells subcutaneously at the back of the neck. These mice were used to assess the sensitivity and cell detection capabilities of MPI and BLI in different imaging conditions (imaging before versus after hair removal, and prone versus supine). All injections were performed under 2% isoflurane anesthesia in 100% oxygen. Each mouse was imaged with MPI and BLI on the same day.

2.6.2. In Vivo MPI

Mice were imaged with MPI first. A full FOV (12 x 6 cm) 2D image was acquired for each mouse in the prone position with high sensitivity scan parameters as outlined previously. To assess MPI signal at different tissue depths, the Balb/c mouse was imaged in the prone and supine position with hair. The MPI signal from the two images was directly compared. Where signal was detected, the iron content and cell number were also quantified using the methods described previously.

2.6.3. In Vivo BLI

Mice were imaged individually with BLI 30-80 minutes after MPI. Mice received an intraperitoneal injection of 150 µL of D-luciferin (30 mg/mL). Each mouse was imaged for 20-25 minutes by taking a series of images with a 2-minute delay. A representative optical image was taken of each mouse to provide anatomical information. It was also possible to acquire x-ray images using the IVIS system for additional anatomical information. The nu/nu mice (one containing 6,400 cells, and one containing 12,800 cells) were imaged in the prone position until the peak radiance was reached. The nu/nu mouse containing 12,800 cells was flipped to the supine position and additional images were acquired to assess the effects of tissue attenuation. The BLI signal in the prone image was compared to the supine image.
For 10 minutes, the C57Bl/6 and Balb/c mice with 12,800 cells were imaged in the prone position with hair. Then, the image acquisition was briefly paused, and the mice were shaved and nair was applied to expose the skin around the injection site. This was done to directly compare the BLI signal with and without hair. The imaging sequence then continued until the peak radiance was reached. We anticipated the peak radiance to arrive 20-25 minutes after the injection of d-luciferin for each mouse.

2.7. Image Analysis

MPI data sets were visualized and analyzed using the HorosTM imaging software. Horos is an open-source program that is distributed free of charge under the LGPL license at https://Horosproject.org and sponsored by Nimble Co LLC d/b/a Purview in Annapolis, MD, USA.
Images of free ProMag and labeled cell samples were analyzed using the standard deviation of an image of the empty sample holder. This standard deviation was multiplied by five. This threshold was applied to select a region of interest (ROI) which was used to quantify the images of free ProMag and labeled cell samples. The total MPI signal (A.U) was calculated by multiplying the ROI area (mm2) by the mean MPI signal (A.U).
For in vivo MPI images, the five times standard deviation method was not used to quantify MPI signal. This is because impeding gastrointestinal signal in some images could also be quantified above this threshold. Instead, a small ROI was drawn around the cell sample in the image excluding the gut region. The maximum signal from the cell sample was recorded. Then, a new ROI was drawn with a threshold of half the maximum signal and the area (mm2) and mean signal (A.U) were multiplied to quantify total MPI signal (A.U).
BLI images were analyzed using the Living Image (Revvity) software. For images of cell samples, an identical ROI was placed over each sample to encircle the region of signal. The radiance (p/sec/cm2/sr) was recorded for each ROI.
All mouse BLI images were analyzed using the same scale. This was done by manually adjusting the maximum and minimum radiance values for each image until they were all the same. An ROI with a unique area was applied for each mouse to encircle the region of signal. For mice where two images were compared (before and after hair removal), an ROI with the same area was used.

2.8. Statistics

All statistical analyses were performed using the GraphPad Prism version 10 program. A linear regression was performed to create a calibration line comparing ProMag content to MPI signal. A two-way ANOVA test was used to assess differences in the BLI signal of ProMag-labeled and unlabeled cell samples. For labeled cell samples, linear regressions were performed to assess the relationship between cell number and BLI signal or MPI signal. To determine the accuracy of cell number calculations for in vitro MPI, a student’s T test with a 95% confidence interval was used to compare the average calculated cell number to the actual cell number for each group of samples: 51,200 – 3,200 cells (n=3 for each cell number, 15 samples total). A correlation plot was created to compare the MPI signal (A.U) and the BLI signal (p/sec/cm2/sr) for each cell sample between 51,200 – 3,200 cells (n=3 for each cell number). Statistical significance was defined by p-values less than 0.05, and the goodness of fit was determined by the r2 value.

3. Results

3.1. Characterization of 4T1 Fluc Transduction and ProMag-Labeling

4T1 cells were transduced to express fluc, sorted, and then labeled with ProMag for dual BLI and MPI. Cells were sorted based on GFP fluorescent intensity (Figure 1A). A GFP sort gate was created by comparing untransduced 4T1 cells to 4T1 luc GFP+ cells. 87.8% of sorted cells were GFP+. These cells were then expanded in culture for 5 days and resorted with a sytox blue viability dye to select live and GFP+ cells (Figure 1B). Pre-sort analysis revealed that 96.0% of the total cell population was viable (sytox blue negative). A post-sort purity analysis revealed that 99.7% of live cells were GFP+. Fluorescent images of sorted cells in culture visually confirmed the high proportion of GFP+ cells (Figure 1C).
A qualitative assessment of labeling efficiency was performed with PPB staining. ProMag was visualized within cells with little presence of unlabeled cells and extracellular iron (Figure 1D). After magnetic column separation, between 5-10% of the total cell population was lost as assessed by cell counting with trypan blue exclusion. Between 90-95% of the total cell population was labeled and remained after magnetic column separation (Table A1-A3, appendix 1). Both methods (PPB and cell counting) showed a high cell labeling efficiency.
The BLI signal from ProMag labeled and unlabeled cells were compared as a measure of cell viability (Figure 1E). There were no significant differences in average radiance between labeled and unlabeled cells, suggesting no effects of ProMag labeling on cell viability (Figure 1F).

3.2. Characterization of ProMag

The MPI performance of ProMag was characterized by MPI relaxometry using the scanner’s RELAX module. The sensitivity of ProMag was 0.0465 A.U. This value is the peak amplitude of the PSF normalized to iron mass (μg), to allow comparing to other SPIOs (Figure 2A). A second relaxometry curve measuring MPI signal normalized to iron mass and maximum signal was used to determine the resolution of ProMag (Figure 2B). The resolution of ProMag was 7.94 mm, which was determined by dividing the FWHM of the PSF (0.0242 T) by the gradient field strength (3.055 T/m). A calibration line revealed a linear relationship between ProMag iron mass and MPI signal (Figure 2C, R2 = 0.9802, p<0.0001). Figure 2D shows the images of each ProMag sample used for the calibration line, displayed in full dynamic range.

3.3. In Vitro Bioluminescence Imaging

Suspended cell samples were first imaged with BLI, then MPI, on the same day (30 samples total). Representative images of 51,200 to 3,200 cells (Figure 3A) and 1,600 to 100 cells (Figure 3B) show that all cell samples produced BLI signal. Radiance values showed a significant linear and positive correlation with increasing cell number for samples between 51,200 – 3,200 cells (Figure 3C, p<0.0001) and 1,600 – 100 cells (Figure 3D, p<0.0001).

3.4. In Vitro Magnetic Particle Imaging

The iron loading per cell was 16.2 ± 0.89 pg. MPI images of 500,000 cell samples used for this calculation are shown in appendix 1 (Figure A1). As few as 3,200 ProMag-labeled cells (51.9 ng of iron) were detected with a 2D scan. The 1,600 cell samples could not be accurately quantified in 2D due to image noise. Detection limits were improved to as few as 800 cells (13.0 ng of iron) using a 3D scan (Figure 4A). 2D and 3D images of cell samples were considered detectable if the signal to noise ratio exceeded five times the standard deviation of the background noise.
For 2D images, the total MPI signal was linearly and positively correlated with increasing cell number (Figure 4B). Using the slope of a 2D calibration line and the total MPI signal, the iron content of each 2D image was calculated. As expected, there was an approximate 50% increase in iron content with each increasing cell number (Figure 4C). The iron content of each 2D image was then divided by the average iron loading per cell to obtain a calculated cell number. There were no significant differences between calculated and actual cell number, where calculated cell number was always underestimated (Figure 4D). The percent difference between the average calculated cell number and the actual cell number was quantified for each group of cell samples imaged with 2D MPI. The highest difference between calculated and actual cell number was 14.1% for 12,800 cells, and the lowest difference was 4.70% for the 6,400 cells (Figure 4E).
A correlation plot was generated to compare the in vitro BLI signal and total MPI signal of each cell sample between 51,200 and 3,200 cells (Figure 5). A linear relationship was observed between the two measurements as cell number increased (R2 = 0.9904, p<0.0001).

3.5. In Vivo Bioluminescence Imaging and Magnetic Particle Imaging

Two nu/nu mice, one injected with 6,400 labeled cells, and the other with 12,800 labeled cells, were imaged with MPI and BLI to compare cell detection limits in vivo (Figure 6). 6,400 cells was selected as the lower limit as it represents one step above the 2D in vitro MPI detection limit of 3,200 cells and we expected lower sensitivity in vivo. In the MPI image, there was a large signal from the gastrointestinal region which prevented the visualization of the smaller region of signal from the injected cells (Figure 6A). This unwanted signal has been observed before [4,38,42]. The interference with other signals of interest is due to the known low dynamic range in MPI [43]. When this nu/nu mouse was imaged with BLI in the prone position, signal from 6,400 cells was clearly visualized and quantified (6.38 x 104 p/sec/cm2/sr) (Figure 6B). Another nu/nu mouse was imaged after receiving an injection of 12,800 labeled cells. This cell number was selected to determine if a higher signal from the cells reduced shadowing from the gut signal. Doubling the cell number allowed for visualization and quantification of the signal from these cells in the 2D full FOV MPI image (Figure 6C). BLI signal was also detected for the same mouse (4.77 x 105 p/sec/cm2/sr) (Figure 6D).
To assess the sensitivity of BLI for mice with hair, one C57Bl/6 mouse with black hair, and one Balb/c mouse with white hair were both imaged after an injection of 12,800 labeled cells (Figure 7). White fur permitted the visualization of signal (1.27 x 105 p/sec/cm2/sr) (Figure 7A); However, it doubled immediately after hair removal (2.41 x 105 p/sec/cm2/sr) (Figure 7B). The signal continued to peak after hair removal (4.02 x 105 p/sec/cm2/sr) (Figure 7C). BLI signal was completely attenuated by the black mouse hair on a C57Bl/6 mouse (Figure 7D). After shaving the BLI signal was visible and measured 1.40 x 105 p/sec/cm2/sr (Figure 7E). The signal similarly continued to peak after hair removal (8.36 x 105 p/sec/cm2/sr) (Figure 7F).
To compare the effect of depth on the sensitivity of MPI and BLI we compared the signals from mice injected with 12,800 cells and imaged in the prone versus supine positions. The mouse neck depth measured 2.5 cm. Figure 8A,B shows that the BLI signal was detected in the prone position but is completely attenuated in the supine position. Figure 8C&D shows that the MPI signal could be detected in both positions. The MPI signal, iron content, and cell number were all similar between prone and supine images. MPI signal was 201 A.U in prone, and 184 A.U in supine. The iron content measured 0.126 μg in prone and 0.115 μg in supine. Finally, the calculated cell number was 7,754 cells in prone, and 7,100 cells in supine.
The tables below list the BLI signal quantification (Table 2) and the MPI signal quantification (Table 3) values for each mouse imaged in this study. These values can be compared to the cell samples imaged previously with both BLI (Figure 3) and MPI (Figure 4). There is a reduction in signal for BLI and MPI when cells are imaged in vivo.
For 12,800 cells, there was an approximate 55% decrease in BLI signal in vivo (n=3 mice) compared to cell samples (n=3) on average. Similarly, the in vivo MPI signal for 12,800 cells (n=3 mice: nu/nu, Balb/c and C57Bl/6) decreased by approximately 49% on average compared to the cell samples (n=3). This MPI signal decrease affected the accuracy of cell number quantification in vivo, and the calculated cell number was 35% - 46% lower than 12,800 (actual cell number injected). Appendix 1 shows the MPI image of the C57Bl/6 mouse injected with 12,800 cells (Figure A2).

4. Discussion

In this study, we compared the sensitivity of MPI and BLI for imaging labeled cells. As expected, with BLI we could clearly detect and quantify the lowest cell number studied which was 100 cells in vitro and 6,400 cells in vivo. These were firefly luciferase expressing cancer cells. The sensitivity of BLI can be improved through alterations to the luciferase - luciferin system to increase the number of photons produced by the reaction. Evans et al. developed an alternative luciferin substrate with a higher affinity for firefly luciferase, which resulted in a greater than 10-fold increase in signal intensity in vivo compared to d-luciferin at the same dose [44]. Hall et al. developed NanoLuc with a 150-fold increase in enzyme specific activity compared to fluc [45]. Maximizing luciferase transcription and/or translation can also increase signal intensity. We employed this strategy by using FACS to select 4T1 cells with the highest expression of the luciferase – GFP construct.
With MPI the lowest cell number detected in vitro was 800 4T1 cells using 3D MPI and 3200 cells using 2D MPI. Comprehensive reporting of MPI cell detection limits should include the imaging parameters, cell number, total amount of iron, iron/cell, SPIO and cell type. The MPI signal will be different for the same cell type labeled with different SPIOs, because some SPIOs produce more signal per mass of iron than others and because the amount of iron loading per cell will differ with different SPIO formulations. The MPI signal will also differ for different cell types labeled with the same type of SPIO, because some cells take up more particles and because the way cells compartmentalize particles can impact the MPI signal [36,37,42].
The 3D detection limit for ProMag labeled 4T1 cells corresponds to ~13 ng of iron or 800 cells labeled with ~16 pg iron /cell, and the 2D detection limit corresponds to ~52 ng of iron or of 3200 cells labeled with ~16 pg iron/cell. For comparison, in a previous study from our lab where 4T1 cells were labeled with a SPIO called Synomag-D the lowest mass of iron detected in vitro with 2D MPI was 28 ng, which corresponded to 8,000 cells labeled with ~3.5 pg of iron/cell [5]. In this case even though a lower amount of iron could be detected the cellular detection limit was worse for Synomag-D. The higher sensitivity in terms of cell number for ProMag labeled 4T1 cells is partly related to the more efficient cell labeling (3.5 pg/cell for Synomag-D versus 16 pg for ProMag). For example, if the cell loading for Synomag-D was 16 pg/cell (like for ProMag) 28 ng would represent 1750 cells. which would be a better cell detection limit compared to ProMag. This is without considering the magnetic properties of Synomag-D compared to ProMag. MPI relaxometry has shown that the peak MPI signal for free Synomag-D is ~3 times higher than ProMag. However, the MPI signal for Synomag-D has been shown to decrease by ~3 times after cell internalization whereas the signal is unchanged for free ProMag versus intracellular ProMag, resulting in the same peak MPI signals for intracellular ProMag and Synomag-D [46].
In another study from our lab 4T1 cells were labeled with a SPIO called Vivotrax. Vivotrax is a ferucarbotran and has been widely used for MPI even though it has a relatively low peak MPI signal, compared to other SPIOs (Synomag-D, MPIO) [6,47]. The 3D detection limit for Vivotrax labeled 4T1 cells was 4000 cells which corresponded to 36 ng of iron (~9.2 pg iron/cell) and 8000 cells with 2D MPI, corresponding to 74 ng of iron. The cellular detection limit was improved for mesenchymal stem cells (MSCs) labeled with Vivotrax. Here the 3D detection limit for Vivotrax labeled MSCs was 2000 cells which corresponded to 38 ng of iron (~19 pg iron/cell) and 4000 cells with 2D MPI, corresponding to 76 ng of iron. The enhanced Vivotrax labeling of MSCs is due to the higher phagocytic capacity and larger size of these cells [42].
In vivo mouse imaging revealed important limitations of both MPI and BLI. The main limitations for in vivo MPI were the low dynamic range and the quantification of cell number. The dynamic range of MPI is limited when multiple samples or signals with different iron concentrations are present in the FOV [43]. In this study, background signal from the gastrointestinal region obscured the lower signal of interest from the 6,400 cells. We have previously shown that images of mouse chow produce MPI signal and that fasting mice can reduce but not eliminate this unwanted signal [4]. Doubling the cell number to 12,800 in another mouse allowed for the detection of signal despite the presence of gut signal. Quantification of the MPI signal, and conversion to iron mass and cell number, was accurate for in vitro imaging of cell samples. However, there was a discrepancy between the number of cells injected into mice and the cell number calculated from the in vivo images. The MPI signal from 12,800 cells injected subcutaneously in vivo was reduced by ~50% compared to the 12,800 cell sample. This agrees with a previous study by our group which found that for mice injected subcutaneously with 100,000 stem cells, the in vivo MPI signal was reduced by ~50% compared to cell pellets [42]. This is likely due to the dispersion of cells from the injection site which reduces the number of cells per voxel leading some cells to fall below the intravoxel detection limit. Particle immobilization in tissue may also contribute to the observed decrease in MPI signal, as reported by Arami et al. for SPIOs in agarose gel mimicking biological tissue [48]. Both of these limitations contribute to the lower cellular detection limit for 2D in vivo MPI (12,800 cells) compared to 2D in vitro MPI (3,200 cells).
The main limitations for in vivo BLI were related to weak signal penetration, signal attenuation and scattering. In our study, black mouse hair completely attenuated the BLI signal from 12,800 cells. This phenomenon has been observed by other groups. Puaux et al. showed that C57Bl/6 mice bearing melanoma tumours demonstrated a 74-fold decrease in BLI signal intensity when they were imaged unshaved, compared to after being shaved [49]. Curtis et al. further reported that after shaving, changes in skin pigmentation over the hair cycle for C57Bl/6 mice also significantly influenced the BLI signal intensity for the same mice imaged over multiple days [50]. For longitudinal cell tracking experiments involving multiple rounds of shaving and skin pigment changes, these drastic changes in BLI signal intensity can affect the validity and interpretation of results. We also found that white mouse hair from a Balb/c mouse caused partial signal attenuation and light scattering. Our results agree with a technical report by Revvity (formerly PerkinElmer), where a tumour-bearing Balb/c mouse showed a 50% increase in BLI signal intensity after hair removal [51]. As has been demonstrated before, mouse hair can interfere with accurate BLI signal measurement, and it should be removed prior to imaging if possible. The challenge of imaging cells in deep tissues is well known for BLI. We demonstrated this by imaging a mouse in both the prone and supine positions. BLI signal could only be detected in the prone position. In the supine position the cells were approximately 2.5 cm deep. There is no attenuation of MPI signal from biological tissue. Signal penetration can be improved for BLI by using a luciferase with a longer peak emission wavelength in the near-infrared spectrum. Akaluc, along with its substrate akalumine-HCl, is an analogue system to fluc and d-luciferin. The akaluc system emits light at a longer wavelength (650 nm) than fluc (600 nm) and can outperform fluc [24,52]. Fluc can also be combined with the akalumine-HCl substrate for improved peak emission wavelength (670 nm) [53] and depth penetration [54], compared to the traditional D-luciferin substrate. However, hepatic background signal and skin toxicity have been reported in mice when using the akalumine-HCl substrate [53]. New luciferase and luciferin pairs are being developed with near-infrared emission spectra to improve the sensitivity and depth penetration of BLI [23].
Although not observed in this study, masking of signal can also occur with BLI. A large primary signal can saturate the CCD camera and prevent the visualization of a dim signal in the same animal. Williams et al. used akaluc BLI and MPI to monitor tumour growth and metastasis. Both modalities detected metastases resulting from a primary mammary fat pad tumour in nude mice; however, they were visualized in different anatomical regions. BLI detected metastases in the upper body, but this required the primary tumour to be covered, without this the strong primary signal masks other signals in the mice. MPI signal was not detected in these regions, presumably due to the dilution of tracer with the proliferation of cancer cells which reduces the amount of iron in the metastatic cells. However, MPI signal was detected in regions closer to the primary tumour, which were obscured in BLI [5]. The discrepancy for locating metastases with MPI and BLI highlights the complementary use of both modalities to give a more complete picture of cell fate.
Like MPI, the BLI signal was also reduced in vivo. For BLI this may be related to access to the luciferin substrates administered intraperitoneally. Cell samples have immediate access to luciferin substrates in vitro, whereas in vivo, luciferin administered intraperitoneally diffuses into tissues and is then delivered through the circulation. Berger et al. found an uneven biodistribution of d-luciferin after intraperitoneal injection, with accumulation in the organs of the gastrointestinal system, the kidneys, and liver after 30 minutes [55]. Evans et al. also compared d-luciferin to a synthetic substrate, CycLuc1, which had a more uniform biodistribution after an intraperitoneal injection and remained in the mouse circulation for longer [44]. With a longer circulation time, more substrate would be delivered to luciferase-expressing cells, thereby increasing the BLI signal intensity. The BLI signal may also be reduced because of cell death which can be caused by the subcutaneous injection. Ultimately this is not as significant a limitation as it is for MPI for which the promise of direct quantification of iron content to estimate cell number.

5. Conclusions

This study explored the advantages and disadvantages of MPI and BLI for imaging labeled cells. The major advantages of MPI include direct cell quantification and zero depth attenuation. MPI has the potential for detecting and quantifying the delivery of therapeutic cells, such as stem cells, or immune cells for cancer therapy, at a designated target site in vivo. SPIOs can also be injected intravenously to be taken up in situ by highly phagocytic cell types, such as macrophages, for measuring inflammation with MPI. The promise of accurate quantification of cell number by MPI in vivo requires further understanding and development of SPIOs and image acquisition and reconstruction methods. The major advantages of BLI include high cellular sensitivity, and the relationship between BLI signal and cell viability. BLI provides dynamic, real-time information about cellular responses in disease models, including cell proliferation, death and migration. This type of information can only be obtained using reporter gene-based imaging at the preclinical level. However, cell number cannot be directly quantified as reporter gene labeling is indirect, and the transcription and/or translation rate will vary from cell to cell. There is no doubt that cellular sensitivity for both modalities will continue to improve with further developments.
Together, MPI and BLI can be used to assess the fate and persistence of an administered population of cells in vivo with high specificity. For instance, MPI can detect signal from small metastases in animals with hair, and at any tissue depth, where these smaller signals may be attenuated when imaging with BLI. Dual cell tracking is also a possibility. For instance, SPIO-labeled T cells can be tracked in a cancer model, and subsequent changes in tumour proliferation or viability can be assessed with BLI. By understanding how these two modalities complement each other, and their individual limitations in sensitivity and cell detection, they can be more efficiently used together for cell tracking.

Author Contributions

Conceptualization, P.J.F. and S.D.T; methodology, P.J.F. and S.D.T.; software, S.D.T.; validation, S.D.T.; formal analysis, S.D.T.; investigation, S.D.T. and B.N.; resources, P.J.F.; data curation, S.D.T.; writing—original draft preparation, S.D.T.; writing—review and editing, P.J.F., S.D.T. and B.N.; visualization, P.J.F. and S.D.T.; supervision, P.J.F.; project administration, S.D.T.; funding acquisition, P.J.F. All authors have read and agreed to the published version of the manuscript.

Funding

This research was funded by the Canadian Institutes of Health Research, grant number PJT 178223 and the National Sciences and Engineering Research Council of Canada, grant number 06671-2020.

Institutional Review Board Statement

The study was conducted in accordance with the Declaration of Helsinki, and approved by the Animal Use Subcommittee of Western University’s Council on Animal Care (AUP # 2023-113, Approved 05/01/2024)

Data Availability Statement

The data presented in this study are available on request from the corresponding author.

Acknowledgments

We would like to acknowledge John J. Kelly and John A. Ronald for providing expertise to guide this project. We would also like to acknowledge the London Regional Flow Cytometry Facility for support and facility use to conduct flow cytometry experiments.

Conflicts of Interest

The authors declare no conflicts of interest. The funders had no role in the design of the study; in the collection, analyses, or interpretation of data; in the writing of the manuscript; or in the decision to publish the results.

Appendix A

Table A1. Cell counts before and after magnetic column separation (trial 1 of 3).
Table A1. Cell counts before and after magnetic column separation (trial 1 of 3).
Cell Count (cells/mL) Before Magnetic Separation Cell Count (cells/mL) After Magnetic Separation
4.75 x 106 4.70 x 106
5.78 x 106 4.61 x 106
3.80 x 106 3.74 x 106
Table A2. Cell counts before and after magnetic column separation (trial 2 of 3).
Table A2. Cell counts before and after magnetic column separation (trial 2 of 3).
Cell Count (cells/mL) Before Magnetic Separation Cell Count (cells/mL) After Magnetic Separation
7.87 x 106 7.01 x 106
7.46 x 106 6.61 x 106
6.72 x 106 6.24 x 106
Table A3. Cell counts before and after magnetic column separation (trial 3 of 3).
Table A3. Cell counts before and after magnetic column separation (trial 3 of 3).
Cell Count (cells/mL) Before Magnetic Separation Cell Count (cells/mL) After Magnetic Separation
4.82 x 106 4.91 x 106
5.88 x 106 5.24 x 106
5.88 x 106 5.65 x 106
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Figure A1. MPI images of triplicate 500,000 cell samples used to calculate the average iron loading per cell.
Figure A1. MPI images of triplicate 500,000 cell samples used to calculate the average iron loading per cell.
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Figure A2. MPI image of C57Bl/6 mouse injected with 12,800 cells. The mouse was imaged with a full FOV in the prone position. The MPI signal (181 A.U), iron content (0.113 μg), and cell number (6,962 cells) were quantified for this mouse.
Figure A2. MPI image of C57Bl/6 mouse injected with 12,800 cells. The mouse was imaged with a full FOV in the prone position. The MPI signal (181 A.U), iron content (0.113 μg), and cell number (6,962 cells) were quantified for this mouse.
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Figure 1. Characterization of 4T1 luc GFP+ cell transduction and ProMag-labeling. (A) A flow cytometry histogram comparing GFP fluorescence for an untransduced 4T1 cell population (grey) and a transduced 4T1 luc GFP+ cell population (blue). A sort gate was created to select the transduced cells based on GFP fluorescent intensity (green). (B) A second flow cytometry histogram showing GFP fluorescence for viable (sytox blue negative) 4T1 luc GFP+ cells. (C) A fluorescent image of sorted 4T1 luc GFP+ cells in culture visually confirms GFP expression (scale bar = 100 μm). (D) A Perls’ Prussian blue stained image of ProMag labeled 4T1 luc GFP+ cells shows minimal extracellular iron and high iron-labeling efficiency (scale bar = 100 μm). (E) BLI image of a 24-well plate with signal from ProMag labeled versus unlabeled cells seeded at different cell number (51,200, 25,600, 12,800 and 6,400 cells). (F) The corresponding radiance measurements for each sample revealed no significant differences between labeled and unlabeled cells (ns = non-significant).
Figure 1. Characterization of 4T1 luc GFP+ cell transduction and ProMag-labeling. (A) A flow cytometry histogram comparing GFP fluorescence for an untransduced 4T1 cell population (grey) and a transduced 4T1 luc GFP+ cell population (blue). A sort gate was created to select the transduced cells based on GFP fluorescent intensity (green). (B) A second flow cytometry histogram showing GFP fluorescence for viable (sytox blue negative) 4T1 luc GFP+ cells. (C) A fluorescent image of sorted 4T1 luc GFP+ cells in culture visually confirms GFP expression (scale bar = 100 μm). (D) A Perls’ Prussian blue stained image of ProMag labeled 4T1 luc GFP+ cells shows minimal extracellular iron and high iron-labeling efficiency (scale bar = 100 μm). (E) BLI image of a 24-well plate with signal from ProMag labeled versus unlabeled cells seeded at different cell number (51,200, 25,600, 12,800 and 6,400 cells). (F) The corresponding radiance measurements for each sample revealed no significant differences between labeled and unlabeled cells (ns = non-significant).
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Figure 2. Characterization of ProMag. (A) A relaxometry curve generated by normalizing MPI signal (A.U) to iron mass (μg) to measure ProMag sensitivity. (B) A second relaxometry curve to measure ProMag resolution. MPI signal was normalized to iron mass and maximum MPI signal. (C) A calibration line showing the linear relationship between iron mass and total MPI signal (R2 = 0.9802, p<0.0001). (D) Corresponding images of ProMag samples used to generate the calibration line, displayed in full dynamic range. Note the differences in scale.
Figure 2. Characterization of ProMag. (A) A relaxometry curve generated by normalizing MPI signal (A.U) to iron mass (μg) to measure ProMag sensitivity. (B) A second relaxometry curve to measure ProMag resolution. MPI signal was normalized to iron mass and maximum MPI signal. (C) A calibration line showing the linear relationship between iron mass and total MPI signal (R2 = 0.9802, p<0.0001). (D) Corresponding images of ProMag samples used to generate the calibration line, displayed in full dynamic range. Note the differences in scale.
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Figure 3. In vitro BLI cell detection. (A) Representative images showing detectable BLI signal for all cell samples from 51,200 to 3,200 cells, and (B) 1,600 to 100 cells. (C) A linear regression showing cell number versus radiance measurements for samples from 51,200 to 3,200 cells (R2 = 0.9787). (D) A linear regression showing cell number versus radiance measurements for samples from 1,600 to 100 cells (R2 = 0.9802). Radiance measurements showed a significant linear and positive correlation with increasing cell number for all samples (p<0.0001).
Figure 3. In vitro BLI cell detection. (A) Representative images showing detectable BLI signal for all cell samples from 51,200 to 3,200 cells, and (B) 1,600 to 100 cells. (C) A linear regression showing cell number versus radiance measurements for samples from 51,200 to 3,200 cells (R2 = 0.9787). (D) A linear regression showing cell number versus radiance measurements for samples from 1,600 to 100 cells (R2 = 0.9802). Radiance measurements showed a significant linear and positive correlation with increasing cell number for all samples (p<0.0001).
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Figure 4. In vitro MPI cell detection. (A) Representative 2D and 3D MPI images of all cell samples that could be detected and quantified. A red “x” is placed over the 2D image of 1,600 cells that could not be accurately quantified due to image noise. (B) A linear regression comparing cell number versus total 2D MPI signal (A.U.) for samples of 51,200 to 3,200 cells. Total 2D MPI signal showed a significant linear and positive correlation with increasing cell number (R2 = 0.9940, p<0.0001). (C) Iron content was calculated for each cell sample that could be quantified in 2D. There was a significant positive and linear correlation between cell number and iron content (R2 = 0.9940, p<0.0001). (D) Using the iron content measurements for each sample, the cell number was calculated and compared to the actual cell number. There was no significant difference between the mean calculated cell number and the actual cell number for each group of samples as determined by student’s T tests (ns = non-significant). (E) A chart was generated to visualize the % differences between the average calculated cell number and the actual cell number for each group of samples. The largest difference was observed for the 12,800 sample group (14.1%) and the smallest difference was observed for the 6,400 cell group (4.70%).
Figure 4. In vitro MPI cell detection. (A) Representative 2D and 3D MPI images of all cell samples that could be detected and quantified. A red “x” is placed over the 2D image of 1,600 cells that could not be accurately quantified due to image noise. (B) A linear regression comparing cell number versus total 2D MPI signal (A.U.) for samples of 51,200 to 3,200 cells. Total 2D MPI signal showed a significant linear and positive correlation with increasing cell number (R2 = 0.9940, p<0.0001). (C) Iron content was calculated for each cell sample that could be quantified in 2D. There was a significant positive and linear correlation between cell number and iron content (R2 = 0.9940, p<0.0001). (D) Using the iron content measurements for each sample, the cell number was calculated and compared to the actual cell number. There was no significant difference between the mean calculated cell number and the actual cell number for each group of samples as determined by student’s T tests (ns = non-significant). (E) A chart was generated to visualize the % differences between the average calculated cell number and the actual cell number for each group of samples. The largest difference was observed for the 12,800 sample group (14.1%) and the smallest difference was observed for the 6,400 cell group (4.70%).
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Figure 5. Correlation plot comparing total MPI signal (x-axis) and radiance (y-axis) measurements for cell samples between 51,200 and 3,200 cells. Each point represents an individual sample (total of 15 samples). There is a strong linear correlation between MPI and BLI signal for in vitro samples (R2 = 0.9904, p<0.0001).
Figure 5. Correlation plot comparing total MPI signal (x-axis) and radiance (y-axis) measurements for cell samples between 51,200 and 3,200 cells. Each point represents an individual sample (total of 15 samples). There is a strong linear correlation between MPI and BLI signal for in vitro samples (R2 = 0.9904, p<0.0001).
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Figure 6. Comparing in vivo cell detection in nu/nu mice. (A) 2D full fov MPI cannot detect signal from 6,400 cells. Note the impeding gastrointestinal signal that is labeled “gut”. (B) A BLI image of the same mouse showing detectable signal from the 6,400 cell injection. This image shows BLI signal overlayed with x-ray. (C) 2D full fov MPI could detect signal from 12,800 cells with impeding gut signal (labeled). (D) BLI signal was detected in the same mouse.
Figure 6. Comparing in vivo cell detection in nu/nu mice. (A) 2D full fov MPI cannot detect signal from 6,400 cells. Note the impeding gastrointestinal signal that is labeled “gut”. (B) A BLI image of the same mouse showing detectable signal from the 6,400 cell injection. This image shows BLI signal overlayed with x-ray. (C) 2D full fov MPI could detect signal from 12,800 cells with impeding gut signal (labeled). (D) BLI signal was detected in the same mouse.
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Figure 7. BLI cell detection in vivo for mice before versus after hair removal. (A) BLI signal is observed in the white mouse with hair. (B) Hair removal reveals an immediate increase in signal. (C) The signal continued to increase after hair removal. (D) Complete signal attenuation was observed for a C57Bl/6 mouse imaged with black hair. (E) BLI signal was observed with hair removal, and (F) continued to increase until reaching peak radiance.
Figure 7. BLI cell detection in vivo for mice before versus after hair removal. (A) BLI signal is observed in the white mouse with hair. (B) Hair removal reveals an immediate increase in signal. (C) The signal continued to increase after hair removal. (D) Complete signal attenuation was observed for a C57Bl/6 mouse imaged with black hair. (E) BLI signal was observed with hair removal, and (F) continued to increase until reaching peak radiance.
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Figure 8. In vivo cell detection and sensitivity with prone and supine imaging for BLI and MPI. (A) In the prone position, signal is detected from 12,800 cells in the nude mouse. (B) This signal is completely attenuated when the mouse is imaged supine (depth of cell injection site = 2.5 cm). A Balb/c mouse containing 12,800 cells had similar MPI signal when imaged in (C) prone and (D) supine.
Figure 8. In vivo cell detection and sensitivity with prone and supine imaging for BLI and MPI. (A) In the prone position, signal is detected from 12,800 cells in the nude mouse. (B) This signal is completely attenuated when the mouse is imaged supine (depth of cell injection site = 2.5 cm). A Balb/c mouse containing 12,800 cells had similar MPI signal when imaged in (C) prone and (D) supine.
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Table 1. Comparison of BLI, PET, SPIO-based MRI, and MPI for cell tracking in animals.
Table 1. Comparison of BLI, PET, SPIO-based MRI, and MPI for cell tracking in animals.
BLI PET MRI MPI
Cell Labeling Agent
Luciferase genes
Positron-emitting
radiotracers		 SPIO SPIO
Source of Signal


 Photons released upon
luciferase – luciferin
enzymatic reaction [23,25]
Emission of two gamma rays via annihilation of positron with an electron in tissue [26]
SPIO effects on surrounding protons producing negative contrast on T2/T2* MRI [34]
 SPIO response to
magnetic fields [37]
Imaging Time






 Seconds – minutes / image (multiple images
per sequence)

15-30 minutes to peak
signal (longer in some cases)
 15 – 30 minutes (3D)

> 60 minutes
(Longitudinal tracer
activity)


 2-10 min (2D)*
10-40 min (3D)*





 2 minutes (2D)
30 minutes (3D)
Number of Mice
Imaged at Once 		Up to 5 mice **
 Up to 4 mice [27] **
 1 mouse
 1 mouse
Longitudinal Cell Tracking
 High (>2 months) [14]

 Low (< 1 week) [26]

 Medium (weeks to months) [17,18]
 Medium (weeks to months) [4,5]
In Vivo Detection Limits



 Single cell [24] in
ideal conditions



 10,000 – 100,000 cells [31] highly dependent on tracer characteristics


 Single cell [35] in
ideal conditions



 1000 cells [56]
(commercial SPIO)

250 cells [40]
(custom SPIO)
Spatial Resolution Low (> 1 mm) [49] High (< 1 mm) [31] High (<1 mm) [34] Low (≥ 1 mm) [37] ***

Quantification



 Total flux (photons/sec)

Average radiance (photons/sec/cm2/steradian)		 Tracer uptake and
specific activity
Area or volume of signal loss, degree of signal loss, change in T2/T2*

 Iron mass (μg) and
cell number
Depth Penetration
 Low (1-2 cm) [25]
 No limitation
 No limitation
 No limitation
Specificity High Medium Low High
*Dependent on imaging sequence, **Dependent on system specifications/setup, ***Can be improved with higher gradient strength.
Table 2. Quantification of BLI radiance (p/sec/cm2/sr) for all mice imaged in this study.
Table 2. Quantification of BLI radiance (p/sec/cm2/sr) for all mice imaged in this study.
Mouse Figure Number of Cells
Injected		 Imaging
Position		 Radiance (p/sec/cm2/sr) Before Hair Removal Radiance (p/sec/cm2/sr) After Hair Removal Peak Radiance (p/sec/cm2/sr)
Nu/nu Figure 6B 6,400 Prone N/A N/A 6.38 x 104
Nu/nu Figure 6D 12,800 Prone N/A N/A 4.77 x 105
Balb/c Figs. 7A, 7B & 7C 12,800 Prone 1.27 x 105 2.41 x 105 4.02 x 105
C57Bl/6 Figs. 7D, 7E & 7F 12,800 Prone Undetectable 1.11 x 105 8.36 x 105
Nu/nu Figure 8B 12,800 Supine N/A N/A Undetectable
Table 3. QQuantification of MPI signal, iron content and cell number for all mice imaged in this study.
Table 3. QQuantification of MPI signal, iron content and cell number for all mice imaged in this study.
Mouse Figure Number of Cells
Injected		 Imaging
Position		 Hair? Total Signal
(A.U)		 Iron Content
(μg)		 Calculated Cell Number
Nu/nu Figure 6A 6,400 Prone Hairless mouse Undetectable N/A N/A
Nu/nu Figure 6C 12,800 Prone Hairless mouse 217 0.135 8,355
Balb/c Figure 8C 12,800 Prone With hair 201 0.126 7,754
Balb/c Figure 8D 12,800 Supine With hair 184 0.115 7,100
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