# Is Subcutaneous Route an Alternative to Intravenous Route for Mouse Contrast-Enhanced Magnetic Resonance Imaging at 1.5 T?

Authors: Jean-Philippe Dillenseger; Christian Goetz; Amira Sayeh; Pierre-Emmanuel Zorn; Stéphane Kremer; Yves Rémond; André Constantinesco; Gaëlle Aubertin-Kirch; Philippe Choquet
Journal: Concepts in Magnetic Resonance Part A
 (2019)

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## Abstract

The present work compares intravenous (IV) and subcutaneous (SC) routes for contrast-enhanced MRI (CE-MRI) in mice. For that purpose, we selected two contrast media used in clinical practice. MRI acquisitions were performed at 1.5 T on five adult mice (Swiss, 41 g +/- 3 g). On each animal, four acquisitions were achieved with IV and SC administration of either Gd-DOTA or MS-325 (1 acquisition per week). For each route, 0.1 mL of NaCl and 0.1 mL of contrast agent were injected. For each acquisition, 200 T1-weighted images were acquired in a 2 h 34 min time lapse. For each route and contrast medium, dynamic contrast enhancement (DCE) curves were obtained. Time-to-peak (TTP), uptake, and washout constant-time values and contrast-to-noise ratio (CNR) were extracted. IV route TTP value was 4.9 min with Gd-DOTA and 5.4 min with MS-325. SC route TTP was 43.3 min with Gd-DOTA and 45.0 min with MS-325. Despite slower uptake constant-time, we show that SC is a potentially valuable alternative to the IV route in mouse preclinical CE-MRI.


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## Body

## 1. Introduction

Multimodal imaging continues to gain popularity in small animal preclinical research, not only because it satisfies the 3Rs principles (reduction, refinement, and replacement) [1–3], but also because it becomes a fundamental tool of translational medicine. In order to maximize translation from mouse to man, it is highly recommended to share common tomographic imaging procedures like single photon emission computed tomography (SPECT), positron emission tomography (PET), X-Ray Computed Tomography (CT), and nuclear magnetic resonance imaging (MRI) data acquisitions [4–6]. As in clinic, contrast agents for CT and MRI are needed in preclinical imaging in order to enhance tissues, organs, vessels, and lesions, and a considerable amount of laboratory engineering effort has been devoted in recent years to that purpose in order to develop specific MRI contrast agents [7–9]. For all that, standard clinical contrast agents [10] are also widely used in preclinical MRI: they are typically small-molecular-weight compounds that distribute nonspecifically in the blood plasma and extracellular space of the body after administration [4]. These compounds have the advantage of being low-cost than specific products and their use perfectly meets translational expectations.One drawback that could critically limit imaging in mice, unlike in humans, is the repeated tail intravenous (IV) puncture, especially when longitudinal procedures are involved. In fact, multiple IV injections result in an increasing risk of tail necrosis around the puncture site [11]. So, it is recommended to carry out the minimum number of needle punctures consistent with good scientific practice. Instead of always using the same puncture site, several different ones should be used along a tail vein [12], which could limit the number of sample times for longitudinal studies. In order to preserve tail veins, subcutaneous (SC) could be an alternative to IV route. To our knowledge, there is no reference describing the use of clinical gadolinium contrast agent for contrast-enhanced MRI (CE-MRI) using the SC route in mice. The aim of this study is to compare IV and SC routes for morphological CE-MRI in mice, with clinical MRI contrast agents with different properties.


## 2. Materials and Methods

### 2.1. MRI System and Acquisition Parameters

#### 2.1.1. MRI System

The MR system (Optimouse 1.5, RS2D, Mundolsheim, France) uses a horizontal magnetic field of 1.5 T delivered by a cryogen free cryocooled actively shielded superconducting magnet (Cryomagnetics, Oak Ridge, USA). Strength of encoding gradients (Magnex Agilent, Santa Clara, CA, USA) is 20 mT/m/A with a maximum reached in 0.1 ms. A 10 cm long bird-cage RF coil (Rapid Biomedical, Würzburg-Rimpar, Germany) of 40 mm diameter was used for mouse imaging. MR series in DICOM format are automatically exported to the OsiriX open-source multimodality medical imaging software for further analysis [13].


#### 2.1.2. MRI DCE Acquisition Parameters

For DCE [14–16], dynamic 2D spoiled gradient echo T1-weighted imaging was performed using the keyhole-imaging technique [17, 18]. Acquisition parameters are summarized in Table 1. In order to follow the contrast media enhancement over a sufficient period of time, 200 images were acquired in 2 h 34 min, for each animal and each protocol.Table 1
Acquisition parameters for dynamic CE-MRI imaging.
Parameters Values Sequence type Spoiled gradient recalled echo-2D TR/TE/FA 25ms / 4ms / 90° Slice thickness 1.75 mm Orientation Coronal FOV dimensions (read x phase) 80 x 40 mm2 Reconstructed matrix size 128 x 64 Reconstructed pixel size 0.625 x 0.625 mm2 Readout BW 30 kHz Nex 6 Image acquisition time 4.8 s Total image number 200 Acquisition rate for images 1-50 12.5 images per min Acquisition rate for image 51-200 1 image per min Total acquisition duration 2h 34min


### 2.2. MRI Contrast Agents

The characteristics of the two contrast agents used in this study are summarized in Table2.Table 2
Dotarem and Vasovist MRI contrast agent characteristics [10].
Contrast agent (trade name) Dotarem Vasovist Molecule name Gadoterate meglumine Gadofosveset trisodium Acronym Gd-DOTA MS-325 Manufacturer Guerbet Bayer Schering Human body region(s) approved CNS, whole body Vessels Approved dose (mmol/kg) 0.1 – 0.3 0.03 Concentration 0.5 mol/L 0.25 mol/L Charge Ionic Ionic Molecular structure Cyclic Linear Osmolality (mOsm/kg H2O at 37°C) 1350 825 Viscosity (mPa.s at 37°C) 2.0 2.1 Plasmatic relaxivities (r1/r2 1.5T in L.mmol−1.s−1) (3.4-3.8)/(3.4-5.2) (18-20)/(32-36)


#### 2.2.1. Dotarem (Gd-DOTA)

Gd-DOTA (Dotarem, Guerbet, Roissy, France) is a paramagnetic macrocyclic ionic contrast agent developed for MRI [19–23]. It is a sterile, nonpyrogenic, clear, colorless to yellow, aqueous solution of 0.5 mmol/mL of gadoterate meglumine. Each mL of Gd-DOTA contains 376.9 mg of gadoterate meglumine, 0.25 mg of DOTA, and water for injection. After intravenous injection, it is confined to the extracellular space and shortens the T1 and T2 relaxation times of target tissues. At recommended doses (Table 2), the effect is observed with the greatest sensitivity on T1-weighted sequences [24]. Gd-DOTA does not cross the intact blood-brain barrier and, therefore, does not enhance normal brain tissues or lesions that keep a normal blood-brain barrier, e.g., cysts or mature postoperative scars. However, disruption of the blood-brain barrier or abnormal vascularity allows distribution of gadoterate in lesions such as neoplasms, abscesses, or infarcts.


#### 2.2.2. Vasovist (MS-325)

MS-325 (Vasovist, Bayer Schering Pharma, Berlin, Germany) is a sterile, nonpyrogenic formulation of a stable gadolinium diethylenetriaminepentaacetic acid chelate derivative with a diphenylcyclohexylphosphate group [19–22, 25]. Each mL of MS-325 contains 244 mg of gadofosveset trisodium (0.25 mmol), 0.27 mg of fosveset, and water for injection. Following IV administration, MS-325 binds reversibly to endogenous serum albumin resulting in longer vascular residence time than non-protein binding contrast agents. The binding to serum albumin also increases the magnetic resonance relaxivity and decreases the relaxation time (T1) of water protons in the vicinity resulting in an increase in signal intensity of blood in T1-weighted sequences. In human studies, gadofosveset substantially shortened blood T1 values for up to 4 hours after IV bolus injection [24].


### 2.3. Animal Management

In order to follow the recommendation to reduce the number of individuals proposed by the 3Rs ethical rule, MRI acquisitions were performed on five Swiss mice (male, 41 g ± 3 g; 58-62 weeks old). All experimental procedures were approved by the Institutional Animal Care Committee and were done according to French regulations concerning small animal experimentation. On each animal (n=5), 4 acquisitions were achieved at one-week intervals (1 acquisition per week per mouse):(i)
IV and SC acquisitions with Gd-DOTA administration;(ii)
IV and SC acquisitions with MS-325 administration.For all acquisitions (n=20), mice were kept anesthetized with isoflurane (1–1.5% in air), were monitored (respiration), and warmed at mouse body temperature in imaging cell (Minerve, Esternay, France) positioned at the middle of the MRI coil.


### 2.4. DCE Protocol

For the IV route acquisitions, a needle was placed in a tail vein. For the SC route acquisitions, a catheter was placed at the mediodorsal part of the pelvis. For each route, the injection point was connected to an automatic syringe pump (Harvard Apparatus, Holliston, USA) via catheter tubing. Its length corresponds to a volume of 0.1 mL. The catheter tubing was filled with 0.1 mL NaCl serum and connected to a syringe containing the contrast agent (Figure1). For each route, 0.1 mL NaCl (catheter tubing) followed by 0.1 mL of contrast agent (syringe) was injected in 2 minutes. The DCE MRI sequence and injection started simultaneously.Figure 1
Injection system (white arrow head) positioned nearby the 1.5T preclinical MRI connected to the mouse via intravenous or subcutaneous catheter (black arrow head).


### 2.5. Data Processing

For each route (IV and SC), the DCE data [14] were extracted with the OsiriX region of interest (ROI) enhancement plugin tool [13]. ROIs were drawn around structures of interest (liver, lower vena cava, and muscles) (Figure 2). Mean DCE curves (n= 5 mice) were obtained for each injection route and curve fitting (ProFit, QuantumSoft, Uetikon am See, Switzerland) was done for each organ of interest.Figure 2
Illustration of liver, muscle, and vena cava ROI positions to generate MRI DCE curves (only wash-in part is schematically represented in this illustration).Mean organ uptake and washout constant times were obtained from the fitting curve f(t) (1), derived from a classical monocompartmental model using a bolus extra vascular input function, where TU is the tissue uptake constant time and TW is the corresponding washout constant time. K is a constant depending on both Tu and Tw and the fraction of the administered dose.(1)ft=K·e-t/Tw-e-t/TUFor each organ of interesti (e.g., liver, lower vena cava, and muscles), the mean contrast to noise ratio (mCNRi) was also measured (n= 5 mice), with OsiriX [13], between the first acquisition (t = T0) and the maximum enhanced image set (t = time to peak (TTP)), using the mean ROI value (mROI) and the mean standard deviation (mSD), according to the following formula:(2)mCNRi=mROITTP-mROIT0mSDTTP2+mSDT02


## 2.1. MRI System and Acquisition Parameters

### 2.1.1. MRI System

The MR system (Optimouse 1.5, RS2D, Mundolsheim, France) uses a horizontal magnetic field of 1.5 T delivered by a cryogen free cryocooled actively shielded superconducting magnet (Cryomagnetics, Oak Ridge, USA). Strength of encoding gradients (Magnex Agilent, Santa Clara, CA, USA) is 20 mT/m/A with a maximum reached in 0.1 ms. A 10 cm long bird-cage RF coil (Rapid Biomedical, Würzburg-Rimpar, Germany) of 40 mm diameter was used for mouse imaging. MR series in DICOM format are automatically exported to the OsiriX open-source multimodality medical imaging software for further analysis [13].


### 2.1.2. MRI DCE Acquisition Parameters

For DCE [14–16], dynamic 2D spoiled gradient echo T1-weighted imaging was performed using the keyhole-imaging technique [17, 18]. Acquisition parameters are summarized in Table 1. In order to follow the contrast media enhancement over a sufficient period of time, 200 images were acquired in 2 h 34 min, for each animal and each protocol.Table 1
Acquisition parameters for dynamic CE-MRI imaging.
Parameters Values Sequence type Spoiled gradient recalled echo-2D TR/TE/FA 25ms / 4ms / 90° Slice thickness 1.75 mm Orientation Coronal FOV dimensions (read x phase) 80 x 40 mm2 Reconstructed matrix size 128 x 64 Reconstructed pixel size 0.625 x 0.625 mm2 Readout BW 30 kHz Nex 6 Image acquisition time 4.8 s Total image number 200 Acquisition rate for images 1-50 12.5 images per min Acquisition rate for image 51-200 1 image per min Total acquisition duration 2h 34min


## 2.1.1. MRI System

The MR system (Optimouse 1.5, RS2D, Mundolsheim, France) uses a horizontal magnetic field of 1.5 T delivered by a cryogen free cryocooled actively shielded superconducting magnet (Cryomagnetics, Oak Ridge, USA). Strength of encoding gradients (Magnex Agilent, Santa Clara, CA, USA) is 20 mT/m/A with a maximum reached in 0.1 ms. A 10 cm long bird-cage RF coil (Rapid Biomedical, Würzburg-Rimpar, Germany) of 40 mm diameter was used for mouse imaging. MR series in DICOM format are automatically exported to the OsiriX open-source multimodality medical imaging software for further analysis [13].


## 2.1.2. MRI DCE Acquisition Parameters

For DCE [14–16], dynamic 2D spoiled gradient echo T1-weighted imaging was performed using the keyhole-imaging technique [17, 18]. Acquisition parameters are summarized in Table 1. In order to follow the contrast media enhancement over a sufficient period of time, 200 images were acquired in 2 h 34 min, for each animal and each protocol.Table 1
Acquisition parameters for dynamic CE-MRI imaging.
Parameters Values Sequence type Spoiled gradient recalled echo-2D TR/TE/FA 25ms / 4ms / 90° Slice thickness 1.75 mm Orientation Coronal FOV dimensions (read x phase) 80 x 40 mm2 Reconstructed matrix size 128 x 64 Reconstructed pixel size 0.625 x 0.625 mm2 Readout BW 30 kHz Nex 6 Image acquisition time 4.8 s Total image number 200 Acquisition rate for images 1-50 12.5 images per min Acquisition rate for image 51-200 1 image per min Total acquisition duration 2h 34min


## 2.2. MRI Contrast Agents

The characteristics of the two contrast agents used in this study are summarized in Table2.Table 2
Dotarem and Vasovist MRI contrast agent characteristics [10].
Contrast agent (trade name) Dotarem Vasovist Molecule name Gadoterate meglumine Gadofosveset trisodium Acronym Gd-DOTA MS-325 Manufacturer Guerbet Bayer Schering Human body region(s) approved CNS, whole body Vessels Approved dose (mmol/kg) 0.1 – 0.3 0.03 Concentration 0.5 mol/L 0.25 mol/L Charge Ionic Ionic Molecular structure Cyclic Linear Osmolality (mOsm/kg H2O at 37°C) 1350 825 Viscosity (mPa.s at 37°C) 2.0 2.1 Plasmatic relaxivities (r1/r2 1.5T in L.mmol−1.s−1) (3.4-3.8)/(3.4-5.2) (18-20)/(32-36)


### 2.2.1. Dotarem (Gd-DOTA)

Gd-DOTA (Dotarem, Guerbet, Roissy, France) is a paramagnetic macrocyclic ionic contrast agent developed for MRI [19–23]. It is a sterile, nonpyrogenic, clear, colorless to yellow, aqueous solution of 0.5 mmol/mL of gadoterate meglumine. Each mL of Gd-DOTA contains 376.9 mg of gadoterate meglumine, 0.25 mg of DOTA, and water for injection. After intravenous injection, it is confined to the extracellular space and shortens the T1 and T2 relaxation times of target tissues. At recommended doses (Table 2), the effect is observed with the greatest sensitivity on T1-weighted sequences [24]. Gd-DOTA does not cross the intact blood-brain barrier and, therefore, does not enhance normal brain tissues or lesions that keep a normal blood-brain barrier, e.g., cysts or mature postoperative scars. However, disruption of the blood-brain barrier or abnormal vascularity allows distribution of gadoterate in lesions such as neoplasms, abscesses, or infarcts.


### 2.2.2. Vasovist (MS-325)

MS-325 (Vasovist, Bayer Schering Pharma, Berlin, Germany) is a sterile, nonpyrogenic formulation of a stable gadolinium diethylenetriaminepentaacetic acid chelate derivative with a diphenylcyclohexylphosphate group [19–22, 25]. Each mL of MS-325 contains 244 mg of gadofosveset trisodium (0.25 mmol), 0.27 mg of fosveset, and water for injection. Following IV administration, MS-325 binds reversibly to endogenous serum albumin resulting in longer vascular residence time than non-protein binding contrast agents. The binding to serum albumin also increases the magnetic resonance relaxivity and decreases the relaxation time (T1) of water protons in the vicinity resulting in an increase in signal intensity of blood in T1-weighted sequences. In human studies, gadofosveset substantially shortened blood T1 values for up to 4 hours after IV bolus injection [24].


## 2.2.1. Dotarem (Gd-DOTA)

Gd-DOTA (Dotarem, Guerbet, Roissy, France) is a paramagnetic macrocyclic ionic contrast agent developed for MRI [19–23]. It is a sterile, nonpyrogenic, clear, colorless to yellow, aqueous solution of 0.5 mmol/mL of gadoterate meglumine. Each mL of Gd-DOTA contains 376.9 mg of gadoterate meglumine, 0.25 mg of DOTA, and water for injection. After intravenous injection, it is confined to the extracellular space and shortens the T1 and T2 relaxation times of target tissues. At recommended doses (Table 2), the effect is observed with the greatest sensitivity on T1-weighted sequences [24]. Gd-DOTA does not cross the intact blood-brain barrier and, therefore, does not enhance normal brain tissues or lesions that keep a normal blood-brain barrier, e.g., cysts or mature postoperative scars. However, disruption of the blood-brain barrier or abnormal vascularity allows distribution of gadoterate in lesions such as neoplasms, abscesses, or infarcts.


## 2.2.2. Vasovist (MS-325)

MS-325 (Vasovist, Bayer Schering Pharma, Berlin, Germany) is a sterile, nonpyrogenic formulation of a stable gadolinium diethylenetriaminepentaacetic acid chelate derivative with a diphenylcyclohexylphosphate group [19–22, 25]. Each mL of MS-325 contains 244 mg of gadofosveset trisodium (0.25 mmol), 0.27 mg of fosveset, and water for injection. Following IV administration, MS-325 binds reversibly to endogenous serum albumin resulting in longer vascular residence time than non-protein binding contrast agents. The binding to serum albumin also increases the magnetic resonance relaxivity and decreases the relaxation time (T1) of water protons in the vicinity resulting in an increase in signal intensity of blood in T1-weighted sequences. In human studies, gadofosveset substantially shortened blood T1 values for up to 4 hours after IV bolus injection [24].


## 2.3. Animal Management

In order to follow the recommendation to reduce the number of individuals proposed by the 3Rs ethical rule, MRI acquisitions were performed on five Swiss mice (male, 41 g ± 3 g; 58-62 weeks old). All experimental procedures were approved by the Institutional Animal Care Committee and were done according to French regulations concerning small animal experimentation. On each animal (n=5), 4 acquisitions were achieved at one-week intervals (1 acquisition per week per mouse):(i)
IV and SC acquisitions with Gd-DOTA administration;(ii)
IV and SC acquisitions with MS-325 administration.For all acquisitions (n=20), mice were kept anesthetized with isoflurane (1–1.5% in air), were monitored (respiration), and warmed at mouse body temperature in imaging cell (Minerve, Esternay, France) positioned at the middle of the MRI coil.


## 2.4. DCE Protocol

For the IV route acquisitions, a needle was placed in a tail vein. For the SC route acquisitions, a catheter was placed at the mediodorsal part of the pelvis. For each route, the injection point was connected to an automatic syringe pump (Harvard Apparatus, Holliston, USA) via catheter tubing. Its length corresponds to a volume of 0.1 mL. The catheter tubing was filled with 0.1 mL NaCl serum and connected to a syringe containing the contrast agent (Figure1). For each route, 0.1 mL NaCl (catheter tubing) followed by 0.1 mL of contrast agent (syringe) was injected in 2 minutes. The DCE MRI sequence and injection started simultaneously.Figure 1
Injection system (white arrow head) positioned nearby the 1.5T preclinical MRI connected to the mouse via intravenous or subcutaneous catheter (black arrow head).


## 2.5. Data Processing

For each route (IV and SC), the DCE data [14] were extracted with the OsiriX region of interest (ROI) enhancement plugin tool [13]. ROIs were drawn around structures of interest (liver, lower vena cava, and muscles) (Figure 2). Mean DCE curves (n= 5 mice) were obtained for each injection route and curve fitting (ProFit, QuantumSoft, Uetikon am See, Switzerland) was done for each organ of interest.Figure 2
Illustration of liver, muscle, and vena cava ROI positions to generate MRI DCE curves (only wash-in part is schematically represented in this illustration).Mean organ uptake and washout constant times were obtained from the fitting curve f(t) (1), derived from a classical monocompartmental model using a bolus extra vascular input function, where TU is the tissue uptake constant time and TW is the corresponding washout constant time. K is a constant depending on both Tu and Tw and the fraction of the administered dose.(1)ft=K·e-t/Tw-e-t/TUFor each organ of interesti (e.g., liver, lower vena cava, and muscles), the mean contrast to noise ratio (mCNRi) was also measured (n= 5 mice), with OsiriX [13], between the first acquisition (t = T0) and the maximum enhanced image set (t = time to peak (TTP)), using the mean ROI value (mROI) and the mean standard deviation (mSD), according to the following formula:(2)mCNRi=mROITTP-mROIT0mSDTTP2+mSDT02


## 3. Results

All mice (n=5) survived the experiments. During all MRI acquisitions, mice mean respiratory rate was 110 ± 17 breaths per minutes.TTP, uptake, and washout constant times and mCNR results are summarized in Table3. Figures 3 and 4, respectively, show IV and SC mean enhancement data (±SD) (n= 5 mice) and fitting curves from the related regions (liver, muscle, and lower vena cava).Table 3
TTP and semiquantitative uptake and washout values extracted from DCE analysis.
Contrast agent Fit-curves analysis Intravenous Subcutaneous Liver Muscle Vein Liver Muscle Vein Gd-DOTA (Dotarem) Uptake constant time (min) 1.1 1.1 1.1 37.0 26.3 17.5 Mean uptake 1.1 24.4 (min) Washout constant time (min) 80.0 58.5 81.3 75.8 61.0 120.4 Mean washout (min) 71.9 79.4 Time to peak (TTP) 4.9 4.8 5.0 51.1 39.0 40.0 (min) mean time to peak (mTTP) 4.9 43.3 (min) mCNR (at mTTP) 7.5 2.5 3.5 5.8 1.9 2.7  MS-325 (Vasovist) Uptake constant time (min) 1.1 1.1 1.1 19.6 24.4 20.4 Mean uptake 1.1 21.3 (min) Washout constant time (min) 144.9 114.9 169.5 140.9 106.4 126.6 Mean washout (min) 143.1 120.5 Time to peak (TTP) 5.9 5.3 5.1 44 47 44 (min) Mean time to peak (mTTP) 5.4 45.0 (min) mCNR (at mTTP) 10.5 9.4 20.1 10.6 13.6 18.9Figure 3
DCE data ± SD (in colors) and fitting curves (black continuous lines) of liver, muscle, and lower vena cava enhancement after IV injection of 0.1 mL of Gd-DOTA (Dotarem) and MS-325 (Vasovist).Figure 4
DCE data ± SD (in colors) and fitting curves (black continuous lines) of liver, muscle and lower vena cava enhancement after SC injection of 0.1 mL of Gd-DOTA (Dotarem) and MS-325 (Vasovist).


### 3.1. Uptake Constant Time and TTP Results

All mean values ± SD were obtained on 5 mice. IV route mean uptake constant times were the same for Gd-DOTA and for MS-325: 1.1 min. The SC route mean uptake constant time was 24.4 min with Gd-DOTA and 21.3 min with MS-325. IV route mean TTP was 4.9 min with Gd-DOTA and 5.4 min with MS-325. The SC route mean TTP was 43.3 min with Gd-DOTA and 45.0 min with MS-325.


### 3.2. Washout Constant Time Analysis

All mean values ± SD were obtained on 5 mice. IV route mean washout constant time was 71.9 min with Gd-DOTA and 143.1 min with MS-325. SC route mean washout constant time was 79.4 min with Gd-DOTA and 120.5 min with MS-325. Results verify that MS-325 is a specific contrast agent with a longer vascular residence time [19–22, 25].


### 3.3. mCNR Results

mCNR values were, for each ROI, lower with Gd-DOTA compared to MS-325 (Table3). No major mCNR differences were observed between IV and SC routes. Figure 5 presents images at T0 and TTP following IV/SC administration of Gd-DOTA/MS-325.Figure 5
MR images obtained at T0 and TTP. Gd-DOTA IV (a) and SC (b) routes; MS-325 IV (c) and SC (d) routes. Windowing was done on the TTP image full dynamic scale and applied to the T0 image.
(a) (b) (c) (d)Figure6 (and S1 and S2) shows head and neck MR angiographic images obtained with MS-325 via SC and IV administration routes, respectively. The DCE MRI scan delay was adapted for each route, in order to reach the maximum contrast enhancement at mid-acquisition. mCNR values between muscle and right jugular vein were 5.1 in SC route (Figure 6(a)) versus 6.2 in IV route (Figure 6(b)).Figure 6
MIP view of the head of a mouse following SC (a) and IV (b) injection of MS-325 (Vasovist), and curves showing the delay from administration and duration of MR acquisition (seeS1 and S2). Acquisition parameters were presented in (c).


## 3.1. Uptake Constant Time and TTP Results

All mean values ± SD were obtained on 5 mice. IV route mean uptake constant times were the same for Gd-DOTA and for MS-325: 1.1 min. The SC route mean uptake constant time was 24.4 min with Gd-DOTA and 21.3 min with MS-325. IV route mean TTP was 4.9 min with Gd-DOTA and 5.4 min with MS-325. The SC route mean TTP was 43.3 min with Gd-DOTA and 45.0 min with MS-325.


## 3.2. Washout Constant Time Analysis

All mean values ± SD were obtained on 5 mice. IV route mean washout constant time was 71.9 min with Gd-DOTA and 143.1 min with MS-325. SC route mean washout constant time was 79.4 min with Gd-DOTA and 120.5 min with MS-325. Results verify that MS-325 is a specific contrast agent with a longer vascular residence time [19–22, 25].


## 3.3. mCNR Results

mCNR values were, for each ROI, lower with Gd-DOTA compared to MS-325 (Table3). No major mCNR differences were observed between IV and SC routes. Figure 5 presents images at T0 and TTP following IV/SC administration of Gd-DOTA/MS-325.Figure 5
MR images obtained at T0 and TTP. Gd-DOTA IV (a) and SC (b) routes; MS-325 IV (c) and SC (d) routes. Windowing was done on the TTP image full dynamic scale and applied to the T0 image.
(a) (b) (c) (d)Figure6 (and S1 and S2) shows head and neck MR angiographic images obtained with MS-325 via SC and IV administration routes, respectively. The DCE MRI scan delay was adapted for each route, in order to reach the maximum contrast enhancement at mid-acquisition. mCNR values between muscle and right jugular vein were 5.1 in SC route (Figure 6(a)) versus 6.2 in IV route (Figure 6(b)).Figure 6
MIP view of the head of a mouse following SC (a) and IV (b) injection of MS-325 (Vasovist), and curves showing the delay from administration and duration of MR acquisition (seeS1 and S2). Acquisition parameters were presented in (c).


## 4. Discussion

### 4.1. IV Tail Puncture in Mice

Nowadays, the IV route is by far and away the most frequently used in humans for contrast agent administration in most current procedures. IV route is also used in laboratory animals [12]; however, repeated tail vein punctures present some limits.(i)Repeatability. In mice, IV tail puncture is poorly reproducible over time due to tail necrosis around the puncture sites [11]. This fact limits longitudinal follow-up studies with imaging and even more, multimodal protocols which require deliveries of both tracers and contrast agents for the acquisition of both functional and morphological data. In fact, in human beings, similar difficulties could occur, as repeated vein punctures impose frequent changes of puncture localisations (e.g., hand dorsal veins, upper limb basilic or cephalic vein) and so could require the surgical creation of an arteriovenous fistula, for instance, in the case of haemodialysis [26].(ii)Technical Limits. With small diameter and fragile vessels, vein puncture could be complex, requires experienced practitioners, and, hence, is operator dependent. A dedicated appropriate workspace is needed to achieve successful punctures in proper conditions [12]. Some research papers tested several small injection ports [27] and presented the developments of automated puncture systems based on vision and/or pressure feedback [11, 28], which could be an interesting alternative to manual puncture.(iii)Physiological Limits. Conventionally, injected contrast media volume is limited by the animal/patient weight. In mice, IV volumes considered good practice are up to 5 ml.kg−1 [12, 29]. In the preclinical field, it is difficult to optimize injected volumes, especially in the case of multimodal protocols involving the use of different contrast agents or tracers. Avoiding the IV route, at least for one compound, is an advantage by limiting the role amount injected liquid.(iv)Reproducibility. In the preclinical field, technical and physiological limits could have an impact on reproducibility [30, 31]. For instance, in practice, it is difficult to ensure that the entire volume is delivered in the vascular compartment only, due to the possibility of extravasation.All these constraints induce limitations or introduce drawbacks in multimodal imaging and/or longitudinal follow-up. Nowadays, multimodal preclinical platforms with MRI and SPECT or PET are expanding rapidly. They are designed with separated apparatus [32, 33] or combined apparatus [4, 5]. In this context, in order to save the use of the tail veins exclusively for radioactive tracer administration for SPECT or PET imaging, the question we seek to answer is whether the SC route could be an alternative to an IV injection during multimodal proceedings involving T1w MRI acquisitions.


### 4.2. The SC Route: An Overview

The chemical, physical, and physiological properties of the SC injection route are complex and unclear [34]. The fact remains is that the SC route is used as an interesting way for drug delivery in human beings in many fields (e.g., IgC therapy, insulin-dependent therapy, palliative care, and anemia treatment) [35–38]. Nevertheless, in clinical medical imaging, except for lymphoscintigraphy [39], it is poorly described in the relevant literature. In contrary, in small animal imaging, we found a large number of studies that used SC delivery for manganese-based contrast agent especially for mouse or rat brain imaging [40–46] but also for implanted tumours [43, 47]. SC deliveries were also described for iron-based particles for lymph node or tumour imaging [48, 49]. Dual-doped nanorods or nanospheres for imaging and drug delivery also used SC delivery [50, 51] as well as surface modified or multivesicular liposomes containing Gd-DTPA and drugs [52, 53]. Gadolinium liposomal contrast agents were also developed for lymph node MRI [54]. All the previously mentioned contrast media were developed for preclinical research more to target fundamental biological processes than to be used in humans. No studies have yet described the SC use of clinical gadolinium contrast agent for small animal imaging. However, this type of administration presents several advantages in preclinical research:(i) First, using clinical gadolinium-based agents in preclinical imaging could facilitate result transfers from mouse to man.(ii) Second, a SC puncture is easy to do technically and, because the SC space is a virtual space, it can also be an excellent site for larger volume fluid delivery: up to 10 mL.kg−1 [12, 29].


### 4.3. Result Analysis and Practical Consequences

We demonstrate with dynamic CE-MRI curves that SC administration is a potential alternative to the IV route in preclinical imaging. Injection route directly impacts mean uptake constant times and as a consequence TTP values. Mean TTP values were in the range between 4,8 and 5,9 min in IV route and between 39 and 47 min in SC route. Concerning mCNRT0-TTP, the MS-325 contrast agent gives higher values than Gd-DOTA for each route (Table 3). This is explained by the higher plasmatic longitudinal relaxivity of MS-325 (Table 2). mCNR results are similar for each route with MS-325, which can be partly accounted for by the fact that MS-325 has a longer vascular residence time [20, 21, 25]. For Gd-DOTA, the SC route quantitatively presents lower mCNRT0-TTP values (-23%) than the IV route (Table 3), due to the shorter vascular residence time of this contrast agent [19–23]. In any case, at TTP, contrast enhancement with Gd-DOTA can clearly be seen for both routes (Figure 5).One observation is still pending: in IV route, the maximum venous enhancement (at TTP) is relatively higher with Gd-DOTA than with MS-325 (Figure3), whereas the latter has a higher plasmatic relaxivity (Table 2). Our work consists in comparing two different routes (IV and SC): this observation does not affect its main conclusions.Knowing the SC, TTP mean value may be interesting in daily practice, in helping for contrast enhanced MRI while preserving the animal’s tail. TTP value allows time between administration and acquisition. The IV route can thus be saved for compounds that need to be administered via this route (e.g., radiotracers). By keeping the SC route for MRI and the IV route for SPECT or PET, it is easy to complete both kinds of explorations in the same time lapse. In daily practice, the SC route allows to save the time initially required for the placement of a venous catheter (if no other injection is needed). From a technical point of view, a SC puncture is easier than an IV puncture; as a consequence SC is potentially more repeatable and reproducible.


### 4.4. Considerations on the Intraperitoneal (IP) Route

The IP route is another administration route, widely used in small animals [12] which could also be an alternative for repeated IV tail punctures. From a technical viewpoint, this administration mode is simpler than IV puncture but more challenging than the SC route.In fact, although the IP route is considered a routine route of administration in rodents, it has several limitations and potential risks [55, 56]. These include pain, potential peritoneum irritation, formation of adhesions within the abdominal cavity, and needle perforation (organs, bowels, and abdominal vessels) [15, 55]. In addition, repeated administration may result in cumulative irritant effects and needle-induced damage [29]. Furthermore, IP administration might result in injection into muscle, subcutaneous tissue, and the intestine and other organs rather than injection exclusively into the peritoneal cavity. Underestimation of the number of failures is also suspected [55].Also, the presence of contrast agent in the peritoneal cavity may, if the study concerns the abdominal-pelvic region, interfere with the analysis of contrast enhancement of vascular or pathological structures (e.g., mice models with intra-abdominal tumours).Furthermore, careful aseptic conditions are needed, as well are operators that are well trained in the handling and restraint of laboratory animals [57].Although IP delivery is a parenteral route of administration, the pharmacokinetics of substances administered intraperitoneally are more akin to those observed after oral administration: the primary route of absorption is via the mesenteric vessels, which drain into the portal vein and pass through the liver [12, 58].


## 4.1. IV Tail Puncture in Mice

Nowadays, the IV route is by far and away the most frequently used in humans for contrast agent administration in most current procedures. IV route is also used in laboratory animals [12]; however, repeated tail vein punctures present some limits.(i)Repeatability. In mice, IV tail puncture is poorly reproducible over time due to tail necrosis around the puncture sites [11]. This fact limits longitudinal follow-up studies with imaging and even more, multimodal protocols which require deliveries of both tracers and contrast agents for the acquisition of both functional and morphological data. In fact, in human beings, similar difficulties could occur, as repeated vein punctures impose frequent changes of puncture localisations (e.g., hand dorsal veins, upper limb basilic or cephalic vein) and so could require the surgical creation of an arteriovenous fistula, for instance, in the case of haemodialysis [26].(ii)Technical Limits. With small diameter and fragile vessels, vein puncture could be complex, requires experienced practitioners, and, hence, is operator dependent. A dedicated appropriate workspace is needed to achieve successful punctures in proper conditions [12]. Some research papers tested several small injection ports [27] and presented the developments of automated puncture systems based on vision and/or pressure feedback [11, 28], which could be an interesting alternative to manual puncture.(iii)Physiological Limits. Conventionally, injected contrast media volume is limited by the animal/patient weight. In mice, IV volumes considered good practice are up to 5 ml.kg−1 [12, 29]. In the preclinical field, it is difficult to optimize injected volumes, especially in the case of multimodal protocols involving the use of different contrast agents or tracers. Avoiding the IV route, at least for one compound, is an advantage by limiting the role amount injected liquid.(iv)Reproducibility. In the preclinical field, technical and physiological limits could have an impact on reproducibility [30, 31]. For instance, in practice, it is difficult to ensure that the entire volume is delivered in the vascular compartment only, due to the possibility of extravasation.All these constraints induce limitations or introduce drawbacks in multimodal imaging and/or longitudinal follow-up. Nowadays, multimodal preclinical platforms with MRI and SPECT or PET are expanding rapidly. They are designed with separated apparatus [32, 33] or combined apparatus [4, 5]. In this context, in order to save the use of the tail veins exclusively for radioactive tracer administration for SPECT or PET imaging, the question we seek to answer is whether the SC route could be an alternative to an IV injection during multimodal proceedings involving T1w MRI acquisitions.


## 4.2. The SC Route: An Overview

The chemical, physical, and physiological properties of the SC injection route are complex and unclear [34]. The fact remains is that the SC route is used as an interesting way for drug delivery in human beings in many fields (e.g., IgC therapy, insulin-dependent therapy, palliative care, and anemia treatment) [35–38]. Nevertheless, in clinical medical imaging, except for lymphoscintigraphy [39], it is poorly described in the relevant literature. In contrary, in small animal imaging, we found a large number of studies that used SC delivery for manganese-based contrast agent especially for mouse or rat brain imaging [40–46] but also for implanted tumours [43, 47]. SC deliveries were also described for iron-based particles for lymph node or tumour imaging [48, 49]. Dual-doped nanorods or nanospheres for imaging and drug delivery also used SC delivery [50, 51] as well as surface modified or multivesicular liposomes containing Gd-DTPA and drugs [52, 53]. Gadolinium liposomal contrast agents were also developed for lymph node MRI [54]. All the previously mentioned contrast media were developed for preclinical research more to target fundamental biological processes than to be used in humans. No studies have yet described the SC use of clinical gadolinium contrast agent for small animal imaging. However, this type of administration presents several advantages in preclinical research:(i) First, using clinical gadolinium-based agents in preclinical imaging could facilitate result transfers from mouse to man.(ii) Second, a SC puncture is easy to do technically and, because the SC space is a virtual space, it can also be an excellent site for larger volume fluid delivery: up to 10 mL.kg−1 [12, 29].


## 4.3. Result Analysis and Practical Consequences

We demonstrate with dynamic CE-MRI curves that SC administration is a potential alternative to the IV route in preclinical imaging. Injection route directly impacts mean uptake constant times and as a consequence TTP values. Mean TTP values were in the range between 4,8 and 5,9 min in IV route and between 39 and 47 min in SC route. Concerning mCNRT0-TTP, the MS-325 contrast agent gives higher values than Gd-DOTA for each route (Table 3). This is explained by the higher plasmatic longitudinal relaxivity of MS-325 (Table 2). mCNR results are similar for each route with MS-325, which can be partly accounted for by the fact that MS-325 has a longer vascular residence time [20, 21, 25]. For Gd-DOTA, the SC route quantitatively presents lower mCNRT0-TTP values (-23%) than the IV route (Table 3), due to the shorter vascular residence time of this contrast agent [19–23]. In any case, at TTP, contrast enhancement with Gd-DOTA can clearly be seen for both routes (Figure 5).One observation is still pending: in IV route, the maximum venous enhancement (at TTP) is relatively higher with Gd-DOTA than with MS-325 (Figure3), whereas the latter has a higher plasmatic relaxivity (Table 2). Our work consists in comparing two different routes (IV and SC): this observation does not affect its main conclusions.Knowing the SC, TTP mean value may be interesting in daily practice, in helping for contrast enhanced MRI while preserving the animal’s tail. TTP value allows time between administration and acquisition. The IV route can thus be saved for compounds that need to be administered via this route (e.g., radiotracers). By keeping the SC route for MRI and the IV route for SPECT or PET, it is easy to complete both kinds of explorations in the same time lapse. In daily practice, the SC route allows to save the time initially required for the placement of a venous catheter (if no other injection is needed). From a technical point of view, a SC puncture is easier than an IV puncture; as a consequence SC is potentially more repeatable and reproducible.


## 4.4. Considerations on the Intraperitoneal (IP) Route

The IP route is another administration route, widely used in small animals [12] which could also be an alternative for repeated IV tail punctures. From a technical viewpoint, this administration mode is simpler than IV puncture but more challenging than the SC route.In fact, although the IP route is considered a routine route of administration in rodents, it has several limitations and potential risks [55, 56]. These include pain, potential peritoneum irritation, formation of adhesions within the abdominal cavity, and needle perforation (organs, bowels, and abdominal vessels) [15, 55]. In addition, repeated administration may result in cumulative irritant effects and needle-induced damage [29]. Furthermore, IP administration might result in injection into muscle, subcutaneous tissue, and the intestine and other organs rather than injection exclusively into the peritoneal cavity. Underestimation of the number of failures is also suspected [55].Also, the presence of contrast agent in the peritoneal cavity may, if the study concerns the abdominal-pelvic region, interfere with the analysis of contrast enhancement of vascular or pathological structures (e.g., mice models with intra-abdominal tumours).Furthermore, careful aseptic conditions are needed, as well are operators that are well trained in the handling and restraint of laboratory animals [57].Although IP delivery is a parenteral route of administration, the pharmacokinetics of substances administered intraperitoneally are more akin to those observed after oral administration: the primary route of absorption is via the mesenteric vessels, which drain into the portal vein and pass through the liver [12, 58].


## 5. Conclusion

The SC route could be a valuable alternative to the IV route in small-animal CE MRI. This contrast administration route allows, on the one hand, preserving the tail veins of the animal and, on the other, saving the time needed for the placement of a venous catheter. Subcutaneously obtained CE can be as efficient as intravenously obtained enhancement for morphological MRI applications. The SC route can definitely be regarded as a useful choice for preclinical longitudinal studies involving MRI with other modalities that require the use of an IV route (e.g., radiotracer administration in PET or SPECT). The potential of this administration route remains to be evaluated with other MR contrast agents.



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*Source: 7428904-2019-06-13.xml*