1. Biochemistry and Chemical Biology
  2. Microbiology and Infectious Disease

Optimization-by-design of hepatotropic lipid nanoparticles targeting the sodium-taurocholate cotransporting polypeptide

  1. Dominik Witzigmann  Is a corresponding author
  2. Philipp Uhl
  3. Sandro Sieber
  4. Christina Kaufman
  5. Tomaz Einfalt
  6. Katrin Schöneweis
  7. Philip Grossen
  8. Jonas Buck
  9. Yi Ni
  10. Susanne H Schenk
  11. Janine Hussner
  12. Henriette E Meyer zu Schwabedissen
  13. Gabriela Québatte
  14. Walter Mier
  15. Stephan Urban
  16. Jörg Huwyler  Is a corresponding author
  1. University of Basel, Switzerland
  2. University of British Columbia, Canada
  3. University Hospital Heidelberg, Germany
  4. University Hospital Heidelberg, INF, Germany
https://doi.org/10.7554/eLife.42276
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Cite this article
  1. Dominik Witzigmann
  2. Philipp Uhl
  3. Sandro Sieber
  4. Christina Kaufman
  5. Tomaz Einfalt
  6. Katrin Schöneweis
  7. Philip Grossen
  8. Jonas Buck
  9. Yi Ni
  10. Susanne H Schenk
  11. Janine Hussner
  12. Henriette E Meyer zu Schwabedissen
  13. Gabriela Québatte
  14. Walter Mier
  15. Stephan Urban
  16. Jörg Huwyler
(2019)
Optimization-by-design of hepatotropic lipid nanoparticles targeting the sodium-taurocholate cotransporting polypeptide
eLife 8:e42276.
https://doi.org/10.7554/eLife.42276
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Abstract

Active targeting and specific drug delivery to parenchymal liver cells is a promising strategy to treat various liver disorders. Here, we modified synthetic lipid-based nanoparticles with targeting peptides derived from the hepatitis B virus large envelope protein (HBVpreS) to specifically target the sodium-taurocholate cotransporting polypeptide (NTCP; SLC10A1) on the sinusoidal membrane of hepatocytes. Physicochemical properties of targeted nanoparticles were optimized and NTCP-specific, ligand-dependent binding and internalization was confirmed in vitro. The pharmacokinetics and targeting capacity of selected lead formulations was investigated in vivo using the emerging zebrafish screening model. Liposomal nanoparticles modified with 0.25 mol% of a short myristoylated HBV derived peptide, that is Myr-HBVpreS2-31, showed an optimal balance between systemic circulation, avoidance of blood clearance, and targeting capacity. Pronounced liver enrichment, active NTCP-mediated targeting of hepatocytes and efficient cellular internalization were confirmed in mice by 111In gamma scintigraphy and fluorescence microscopy demonstrating the potential use of our hepatotropic, ligand-modified nanoparticles.

https://doi.org/10.7554/eLife.42276.001

Introduction

The design of hepatotropic drug carriers is of great interest for the treatment of various liver disorders (Williams et al., 2014; Poelstra et al., 2012; Reddy and Couvreur, 2011). In particular if cell-type specific delivery of macromolecular therapeutic agents, selective targeting of parenchymal liver cells and internalization is needed. Previously, hepatocyte targeted nanoparticles have been developed exploiting endogenous and exogenous targeting ligand-based mechanisms using glycan, protein or antibody modifications of the nanoparticle surface (Akinc et al., 2010; Akinc et al., 2009; Barrett et al., 2014; Detampel et al., 2014; Witzigmann et al., 2016a). Most established systems for liver-specific drug delivery rely on targeting the hepatic asialoglycoprotein (ASGPR) or low density lipoprotein (LDLR) receptors. However, studies investigating alternative targeting strategies based on other hepatocyte-specific receptors are limited. In this respect, a promising alternative might be offered by the hepatitis B virus (HBV), which shows a pronounced efficacy to infect the human liver due to its strong affinity to hepatocytes. Less than 10 virus particles have been shown to be sufficient to efficiently target hepatocytes of chimpanzees resulting in a pathogenic HBV infection (Asabe et al., 2009). The reason for its extraordinary liver tropism is a highly specific amino acid sequence in the large HBV envelope protein (i.e. HBVpreS1 domain), which is essential for target receptor recognition (Meier et al., 2013; Schieck et al., 2013). For decades, the specific target of HBV on the sinusoidal membrane of hepatocytes was unknown until in 2012 the interaction with the human sodium-taurocholate cotransporting polypeptide (NTCP/SLC10A1) was identified (Yan et al., 2012). Subsequently, Urban and colleagues performed a fine mapping of the HBVpreS sequence to identify the amino acids responsible for efficient binding (Schulze et al., 2010; Ni et al., 2014; Schieck et al., 2013). As a result, the first HBV/HDV entry inhibitor, a myristoylated peptide named Myrcludex B, was developed and successfully introduced in clinics (currently phase II clinical trials) (Blank et al., 2016; Urban et al., 2014). Myrcludex B binds with high affinity and specificity to human NTCP on the sinusoidal membrane of hepatocytes thereby blocking binding of virus particles to their target cells.

Based on these findings, the question arises whether Myrcludex B might serve as a targeting ligand to design a hepatotropic, NTCP-specific nanoparticle. In recent years, several groups have therefore attempted to develop targeting strategies based on HBV envelope proteins, for example recombinant HBV envelope protein particles (bio-nanocapsules) or HBV preS1-derived functionalized liposomes (Liu et al., 2016; Somiya et al., 2016; Somiya et al., 2015; Zhang et al., 2015; Zhang et al., 2014). However, the nanoparticulate drug delivery systems developed had physicochemical properties (e.g. size, colloidal stability, and immunogenic potential), which were sub-optimal for efficient in vivo targeting of hepatocytes. Especially the size of the nano-formulations presented a limitation. Most developed formulations had sizes above the average diameter of hepatic fenestrations in healthy humans (i.e. 100 nm) (Wisse et al., 2008) thereby limiting the passage through liver fenestrations and consequently the access to the space of Disse and the sinusoidal membrane of hepatocytes. Notably, the liver fenestrae diameter of rodents show high species and strain differences ranging from around 100 nm to 160 nm, possibly explaining positive liver targeting of published formulations (Braet and Wisse, 2002; Steffan et al., 1987; Wisse et al., 2008). In addition, a nanoparticle size above 100 nm triggers phagocytosis by cells of the reticuloendothelial system (i.e. hepatic Kupffer cells and spleen macrophages) resulting in rapid blood clearance (Kettiger et al., 2013). Both factors significantly decrease the likelihood of reaching the parenchymal liver tissue and increase the risk for potential off-target effects in untargeted tissues.

Surface properties are another important characteristic of nanoparticles. The surface charge (i.e. ζ potential) should be slightly negative (Xiao et al., 2011) to prevent sequestration of particles in the lung (i.e. due to a positive charge) (Ishiwata et al., 2000) or rapid clearance by cells expressing scavenger receptors (i.e. due to an excessive negative charge) (Rothkopf et al., 2005). According to the classical Derjaguin-Landau-Verwey-Overbeek (DLVO) theory of colloids, a neutral charge has to be avoided to prevent particle agglomeration. In addition to surface charge, steric stabilization by PEGylation mediates long circulating properties and prevents opsonization (Karmali and Simberg, 2011; Milla et al., 2012).

It was the aim of the present study to design and optimize a nanoparticle based on liposomes combined with derivatives of Myrcludex B to efficiently target hepatocytes while minimizing interactions with off-target cell types. Optimization of physicochemical properties of the nanoparticles included size and charge optimization and steric shielding by PEGylation. Derivatives of Myrcludex B were selected based on target binding, cellular uptake and their impact on the colloidal stability of nanoparticles. For the lipid membrane composition, we used a FDA and EMA approved multi-component lipid formulation based on Doxil (i.e. liposomal formulation of doxorubicin) (Barenholz, 2012). To design an optimal targeted system, several Myrcludex B derivatives with variations in the peptide sequence or fatty acid modification were covalently linked to the distal end of PEG-lipids. NTCP-specific and ligand-dependent uptake was confirmed in vitro using human liver-derived cell lines. Recently, Shan et al. reported huge discrepancies between in vitro systems and rodent experiments during the development of targeted nanomedicines (Shan et al., 2015). Therefore, we used the zebrafish as a complementary in vivo screening model based on our previous work (Sieber et al., 2019b; Campbell et al., 2018; Einfalt et al., 2018; Sieber et al., 2017). We assessed the effect of nanoparticles` ligand type and ligand density on their pharmacokinetics. To this end, human-derived cell lines lacking or expressing the human NTCP (hNTCP, SLC10A1) were xenotransplanted into zebrafish embryos prior to systemic administration of nanoparticles. Finally, tissue distribution of dual-labeled nanoparticles was qualitatively (fluorescence-based) and quantitatively (radionuclide-based) investigated in vivo in mice to demonstrate the targeting potential of our hepatotropic nanoparticle platform in higher vertebrates.

Results and discussion

Design and characterization of a hepatotropic nanoparticle for NTCP-specific targeting

The aim of our study was the design of a hepatotropic, targeting ligand-modified nanoparticle. To this end, the surface of liposomal nanoparticles was modified using targeting peptides or lipopeptides derived from the preS1 domain of the HBV large envelope protein (Figure 1A). Based on a previous screening of 26 HBVpreS peptide variants, we selected Myrcludex B, the first HBV entry inhibitor (Blank et al., 2016; Bogomolov et al., 2016), and five additional Myrcludex B-derived peptides to evaluate the influence of amino acid sequence variations or acyl chain modifications on targeting efficiency and thereby optimize our hepatotropic nanoparticle. All Myrcludex B derived (lipo)peptides were synthesized in high yields and purity by standard solid phase peptide synthesis using Fmoc-chemistry (Schieck et al., 2013; Schieck et al., 2010; Müller et al., 2013). Lipopeptides were N-terminally modified with the fatty acids myristic acid (saturated C14) or capric acid (saturated C10), since our previous studies have shown that fatty acid modification is key for mediating interactions with target cells. C-termini of synthesized targeting (lipo)peptides were modified with cysteine residues to allow conjugation to the distal end of PEGylated phospholipids (DSPE-PEG2000-Maleimide) integrated into sterically stabilized liposomes. Coupling was achieved by a chemically reactive maleimide, giving rise to a metabolically stable thioether bond suitable for applications in living organisms (Figure 1A). Successful conjugation of Myrcludex B to lipid-based nanoparticles was demonstrated by fluorescence correlation spectroscopy using Myrcludex B-Atto488. The autocorrelation curve of nanoparticle conjugated peptides showed a significant shift to longer diffusion times as compared to the free peptide, with average diffusion times of τd = 1639 μs and τd = 192 μs, respectively (Figure 1—figure supplement 1).

Figure 1 with 9 supplements see all
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Hepatotropic nanoparticles based on liposomes modified with Myrcludex B-derived peptides for NTCP-specific targeting.

(A) Schematic representation of peptides derived from Hepatitis B virus (HBV) large envelope protein including the first entry inhibitor, Myrcludex B. Different peptides were conjugated via thiol function to the distal end of PEG chains integrated in the nanoparticle structure using maleimide chemistry. The most important amino acid sequence (9-15) for NTCP-specific binding is highlighted in green color in each lipopeptide. (B) Representative transmission electron microscopy images of different Myrcludex B-derived lipopeptide conjugated nanoparticles. Scale bar = 100 nm. (C) Uptake of Myrcludex B-modified nanoparticles into human cells with variable NTCP expression levels. Nanoparticles have a dual fluorescent label, that is lipophilic membrane label (DiI, red) and hydrophilic payload incorporation (carboxyfluorescein, green). Representative confocal laser scanning microscopy maximum intensity projections for Myr-preS2-48 modified nanoparticles after 30 min are shown. Dotted lines indicate cell membranes. Blue signal: Hoechst stain of cell nuclei. Scale bar = 10 µm. (D) Flow cytometry analysis of uptake rate into non-hepatic HeLa cells, liver derived HepG2 cells and SLC10A1 overexpressing HepG2 cells. Increasing concentrations of nanoparticles (CDiI) modified with different Myrcludex B-derived peptides were evaluated. Relative mean fluorescence intensities (MFI) of DiI signals normalized to untreated cells are given. All values are shown as mean ± SD of biological replicates (n ≥ 3 independent experiments). Numerical data for all graphs are shown in Figure 1—source data 1.

https://doi.org/10.7554/eLife.42276.002
Figure 1—source data 1

Characterization of hepatotropic nanoparticles.

https://doi.org/10.7554/eLife.42276.012

Liposome membrane partition coefficients of mono fatty acid modifications are orders of magnitudes lower as compared to di-lipid anchors. (Sauer et al., 2006) Therefore, the distearoyl anchor of DSPE results in a stable incorporation of the PEGylated phospholipid-targeting ligand conjugate in the lipid bilayer of liposomes (membrane partition coefficient >103 mM−1), whereas the PEG linker offers a flexibility to the distally tethered lipopeptides to extend away from the liposome surface. In addition, a thermodynamically favorable backward bending insertion of the acyl chain into the liposomal membrane is possible. A slight change in transition temperature evaluated by pressure perturbation calorimetry and differential scanning calorimetry confirmed this hypothesis (data not shown). The formulation yield of modified nanoparticles after purification was dependent on the conjugated Myrcludex B derived (lipo)peptide with preS2−48 > Myr-preS2−31 > Myr-preS2-48A ≥ Myr-preS2−48 > Cap-preS2-48.

Light scattering and electron microscopy verified that all nanoparticles, that Myrcludex B-derived peptide conjugated liposomes (modified without or with C14 acyl moiety) had a spherical morphology with a small size around 90 nm, narrow size distribution (that is PDI <0.2), and a slightly negative zeta potential (Figure 1B, Table 1). Only a small increase in the hydrodynamic size of about 2 nm was observed after conjugation of Myrcludex B-derived peptides (Table 1). The zeta potential of nanoparticles remained negative due to a negative net charge of Myrcludex B-derived lipopeptides at physiological pH. Thus, the physicochemical properties of nanoparticles were not significantly influenced by the surface modification with HBVpreS derived lipopeptides containing C14 acyl chains. Exceptions were nanoparticles modified with Cap-preS2-48, which had an average diameter of 134.28 nm and a PDI of 0.24 (Figure 1B, Table 1).

Table 1
Physicochemical characteristics of nanoparticles with different surface modifications.

Hydrodynamic size [nm], polydispersity index (PDI), and zeta potential [mV] were analyzed using dynamic and electrophoretic light scattering. All values are shown as mean ± SD of n ≥ 3 independent experiments. Numerical data for all nanoparticles are shown in Table 1—source data 1..

https://doi.org/10.7554/eLife.42276.013
Surface modificationSize [nm] ± SDPDI ± SDZeta potential [mV] ± SD
PEG88.53 ± 5.890.05 ± 0.01−5.93 ± 0.63
preS2-4890.74 ± 5.830.06 ± 0.02−3.34 ± 1.38
Myr-preS2-48 A90.77 ± 4.980.06 ± 0.04−13.35 ± 3.08
Myr-preS2-3189.10 ± 4.380.10 ± 0.02−9.82 ± 0.87
Cap-preS2-48134.28 ± 36.230.24 ± 0.04−8.39 ± 1.13
Myr-preS2-4892.21 ± 6.780.12 ± 0.08−10.70 ± 4.25
Table 1—source data 1

Physicochemical characterization of nanoparticles.

https://doi.org/10.7554/eLife.42276.014

It is tempting to speculate, that the C10 acyl chain of Cap-preS2-48 interfered with liposome membrane stability. As compared to longer acyl chains the backward bending insertion of C10 acyl chains into intra-liposomal membranes is less stable, thus promoting faster dissociation and possible interactions with neighboring liposomes due to re-association with inter-liposomal membranes. This was also indicated by formation of aggregates resulting in shorter storage stability (data not shown). Previously published studies reporting a rapid partitioning of shorter lipid anchors from liposomal vesicles support our observation of unfavorable liposome interactions for Cap-preS2-48 (Sauer et al., 2006; Webb et al., 1998).

Cellular uptake and viability

Next, we investigated the biocompatibility and targeting capacity of our ligand-modified nanoparticles in a panel of three different cell lines in vitro, that is non-hepatic HeLa cells devoid of SLC10A1 (negative control), liver-derived wild type HepG2 cells (HepG2 WT, hepatocyte control cell line with no detectable SLC10A1 expression based on PCR) and HepG2 cells overexpressing the human NTCP (HepG2 SLC10A1). We used lentiviral transduced cells overexpressing SLC10A1 as a positive control to confirm the specificity of our system since human liver derived cell lines such as HepG2 and HuH7 down-regulated NTCP during oncogenic transformation (i.e. NTCP expression levels are significantly decreased in hepatocellular carcinoma) (Lempp et al., 2016). In all cell lines, nanoparticles showed a high cytocompatibility up to the highest tested lipid concentration of 8 mM, which is far beyond liposome blood concentrations achievable in a clinical setting (Figure 1—figure supplement 2 demonstrating no decrease of cell viability using the MTT assay) (Barpe et al., 2010).

In vitro uptake studies revealed that Myrcludex B-modified nanoparticles were rapidly internalized within 30 min into liver-derived HepG2 cell lines whereas no binding or cellular uptake was observed in non-hepatic HeLa cells (Figure 1C, representative confocal laser scanning microscopy images for Myr-preS2-48 modified nanoparticles). Both the liposomal nanoparticle (DiI signal) and the encapsulated payload (carboxyfluorescein (CF) signal), were detected intracellularly. Notably, CF was encapsulated into our nanoparticles at a fluorescence self-quenching concentration (i.e. 60 mM, Figure 1—figure supplement 3). Thus, CF fluorescence increases significantly after overcoming the Förster critical transfer distances, that is release of CF from nanoparticles into surrounding environment (Chen and Knutson, 1988). Specific uptake of nanoparticles with NTCP-binding component preS-peptide was enhanced with increasing SLC10A1 expression levels (Figure 1C,D and Figure 1—figure supplement 4) demonstrating a high target specificity (i.e. HeLa WT <HepG2 SLC10A1). Surprisingly, the highest DiI signal (and not CF signal) in HeLa cells was observed with PEGylated nanoparticles. It is tempting to speculate that nanoparticle modification with Myrcludex B-derived lipopeptides decreases the interaction with negatively charged cell membranes of SLC10A1-deficient cells (e.g. HeLa) due to a negative net charge of lipopeptides at physiological pH and thus increased electrostatic repulsion. Uptake studies with a different liver-derived cell line (HuH7) comparing wild type and SLC10A1 overexpressing cells confirmed the SLC10A1 specific interaction. Overexpression of SLC10A1 again resulted in a strong enrichment of cellular uptake ruling out an involvement of cell-line specific artifacts (Figure 1—figure supplement 5).

In order to demonstrate the potential application of Myr-preS2-31 modified nanoparticles as drug delivery system, we successfully incorporated small molecular payloads as well as larger compounds into nanoparticles payloads (i.e. propidium iodide, doxorubicin, FITC-labeled peptide, DNA vector) to enhance their internalization into NTCP expressing cells (Figure 1—figure supplements 6, 7, 8 and 9). Indeed, time-dependent uptake studies confirmed the rapid binding and internalization process of Myr-preS2-31 modified nanoparticles (Figure 1—figure supplements 6, 7 and 8). Of note, propidium iodide is a cell membrane impermeable drug. Thus, NTCP-targeted nanoparticles enabled internalization into cells and successful release into cytosol indicated by nuclear counterstain (Figure 1—figure supplement 7). To investigate the potential application of NTCP-targeted lipid nanoparticles as gene delivery systems, we encapsulated a DNA vector coding for GFP into lipid nanoparticles based on a clinically approved lipid composition and modified with Myr-preS2-31. High content screening analysis demonstrated that modification of nanoparticles with Myr-preS2-31 significantly increases the transfection of NTCP expressing cells (Figure 1—figure supplement 9). These experiments highlight future applications of the developed carriers and serve as a starting point for future extended in vivo studies in different species and disease models.

Competition of NTCP-specific cellular binding and uptake of targeting ligand-modified nanoparticles

To confirm specificity of NTCP interactions with Myrcludex B derived ligands, we used pre-incubations with free Myrcludex B-Atto565 to competitively inhibit nanoparticle binding and cellular uptake (Figure 2A). Fluorescently labeled Myrcludex B can be considered to be a suitable blocking agent since its binding to NTCP expressing HepG2 SLC10A1 cells results in a significant shift in fluorescence signal as compared to control cells (data not shown). Uptake inhibition of nanoparticles modified with Myr-preS2-31, Cap-preS2-48, and Myr-preS2-48 by free Myrcludex B-fluorescein was confirmed by flow cytometry (Figure 2B). In contrast, the uptake of Myr-preS2-48A modified nanoparticles was not significantly inhibited by free Myrcludex B, due to the non-specific amino acid sequence (see difference in essential amino acid sequence highlighted in Figure 1A). By incubation of cells in presence of NaN3 or at low temperature (i.e. 4°C), we confirmed that the uptake of NTCP targeted nanoparticles is an energy-dependent process (Figure 2A). These results demonstrate that hepatotropism of nanoparticles is mediated by NTCP and that the cellular uptake of the carrier is an active and energy-dependent process.

Figure 2 with 5 supplements see all
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NTCP-specific and ligand-dependent uptake of Myrcludex B-derived lipopeptide conjugated nanoparticles into liver-derived cells in vitro.

(A) Competitive inhibition study of Myrcludex B (MyrB)-conjugated nanoparticle uptake (carboxyfluorescein payload, green signal) into HepG2 SLC10A1 already after 30 min. Free Atto-565 labeled Myrcludex B (red signal) was added after (left panel) or before (middle panel) nanoparticle. Uptake studies at lower temperature (T↓, 4°C, right panel) were performed to demonstrate energy-dependent process of nanoparticle internalization. Representative confocal laser scanning microscopy images are shown. Blue signal: Hoechst stain of cell nuclei. Scale bar = 10 µm. (B) Quantification of nanoparticle uptake in absence or presence of free Myrcludex B dependent on different Myrcludex B derived peptide modification. All values are shown as mean ± SD of biological replicates (n = 3 independent experiments). **p<0.01. (C) Uptake study of nanoparticles (membrane dye, DiI, red signal) loaded with carboxyfluorescein (green signal) into HepG2 SLC10A1 without, mixed or covalently modified with Atto-633 conjugated Myr-preS2-31 (yellow signal). Myr-preS2-31-K-Atto633 is covalently linked to surface via stable thioether bond (right panel). Representative confocal laser scanning microscopy images are shown. Blue signal: Hoechst stain of cell nuclei. Scale bar = 10 µm. (D) Concentration (CLipid) dependent uptake of nanoparticles modified with different amounts of Myr-preS2-31 analyzed by flow cytometry and based on CF signal. All values are shown as mean ± SD of biological replicates (n = 4 independent experiments). *p<0.05, **p<0.01, ***p<0.001. Numerical data for all graphs are shown in Figure 2—source data 1.

https://doi.org/10.7554/eLife.42276.015
Figure 2—source data 1

Influence of ligand on cellular interactions.

https://doi.org/10.7554/eLife.42276.021

Selection of the optimal hepatotropic Myrcludex B-derived lipopeptide

After evaluating the formulation yield, physicochemical characteristics (i.e. storage/colloidal stability, hydrodynamic diameter, size distribution, zeta potential) and the targeting capacity of our NTCP-specific nanoparticles in vitro, we identified Myr-preS2-48 and Myr-preS2-31 as lead structures and used these for further investigations. This choice was based on the following observations:

First, only nanoparticles modified with lipopeptides but not peptides without conjugated fatty acid (e.g. preS2-48) can bind to NTCP. This set of experiments confirmed that the acyl modification of peptides on nanoparticles` surface is a crucial prerequisite for hepatocyte binding as reported recently for free peptides (Meier et al., 2013; Schieck et al., 2013). Only acyl modified peptides increased nanoparticle binding and internalization. Second, liposomes decorated with peptides conjugated to capric acid had a reduced colloidal stability. Their storage stability was limited due to particle aggregation. Furthermore, their size of around 134 nm exceeds the diameter of liver sinusoid fenestrations presumably limiting their access to the space of Disse. Third, Myr-preS2-48A modified nanoparticles were excluded due to poor NTCP specificity as demonstrated by the lack of binding competition by free Myrcludex B. In addition, the uptake of these nanoparticles was independent of NTCP expression levels and even higher in HepG2 wild type cells (Figure 1D).

Mechanistic studies on NTCP mediated cellular binding and internalization

In order to demonstrate the importance of covalent peptide attachment, we used a triple fluorescence labeling strategy (Figure 2C). The targeting ligand Myrcludex B was labeled with Atto633, the liposomal phospholipid bilayer was labeled with DiI, and the aqueous cargo payload of nanoparticles consisted of CF. Myr-preS2-31-K-Atto633 was labeled at an additionally introduced lysine at position 2, in order to still allow conjugation to the nanoparticle surface by the terminal cysteine. Recently, we have shown that additional N-terminal amino acids do not interfere with specific liver enrichment (for comparison Myr-preS−11-48) (Schieck et al., 2013).

First, CF-loaded, DiI-labeled nanoparticles were incubated with Myr-preS2-31-K-Atto633 and purified using size exclusion chromatography to remove free targeting ligand. Cell experiments confirmed successful removal of free Myr-preS2-31-K-Atto633 (no signal on cell membrane) and as expected no uptake of PEGylated nanoparticles. As a control, we added a mixture of free Myr-preS2-31-K-Atto633 and PEGylated nanoparticles to HepG2 SLC10A1 cells without prior purification. Notably, a strong fluorescence signal on the cell membrane was observed due to specific binding of free Myr-preS2-31-K-Atto633 to SLC10A1 indicating specific targeting despite an additional N-terminal amino acid. Free Myr-preS2-31-K-Atto633 did not interact with PEGylated nanoparticles and thus did not trigger nanoparticle entry into HepG2 SLC10A1 cells. Finally, we covalently linked the Myr-preS2-31-K-Atto633 to the nanoparticle surface by Michael addition of the distal cysteine residue to maleimide-functionalized PEGylated phospholipids integrated in the nanoparticle structure. A strong cellular binding and uptake of Myr-preS2-31-K-Atto633 modified nanoparticles was observed already within 1 h.

Interestingly, nanoparticles including their payload entered the target cell whereas the targeting ligand remained on the cell surface. Since Myrcludex B has a remarkably high affinity to the NTCP (KD of 67 nM) (Meier et al., 2013), it is tempting to speculate that the targeting ligand is retained by NTCP on the cell surface while the dissociated liposome payload is internalized and further processed by a yet unknown mechanism. Of note, intracellular CF signals were considerably higher when compared to DiI signals. This might also indicate liposome dissociation and perhaps loss of DiI during the internalization process. Uptake experiments using pharmacological pathway inhibitors suggested a partially clathrin-dependent and caveolin-independent mechanism, which differs from the process of phagocytosis and micropinocytosis (Figure 2—figure supplement 1). Intriguingly, additional factors besides NTCP binding seem to contribute to this process. Non-hepatic HeLa cells transduced with mouse NTCP (mNtcp; Slc10a1) or SLC10A1 can bind Myrcludex B-modified nanoparticles. However, binding is reduced as compared to binding in hepatic cell lines and no uptake is observed (Figure 2—figure supplement 2). Thus, additional hepatic cell dependent factors seem to play a role for efficient binding and internalization. Indeed, Verrier et al. reported recently that glypican five expression is an important co-factor for HBV entry (Verrier et al., 2016). Notably, uptake experiments using psgA745 cells (CHO xylosyltransferase mutants) overexpressing NTCP showed that binding of Myrcludex B alone is not influenced by glycosaminoglycans (Figure 2—figure supplement 3). In sharp contrast, binding of nanoparticles could be partially inhibited in HepG2 WT cells using heparan sulfate suggesting an involvement of glycosaminoglycans in the binding and subsequent internalization process of nanoparticles for hepatic cells (Figure 2—figure supplement 4). Therefore, it will be an important step for the design of next-generation carrier systems to elucidate such co-factors in detail and adapt the nano-sized delivery system accordingly.

To demonstrate concentration-dependent nanoparticle uptake of Myr-preS2-31 and investigate the effect of ligand density, qualitative and quantitative fluorescence techniques were used (Figure 2D). Therefore, we performed in vitro experiments using nanoparticles with variable amounts of coupled Myr-preS2-31 (0 mol% - 0.5 mol% initial maleimide functionalities on nanoparticle surface). With increasing targeting ligand concentration, a significant increase in cellular uptake was observed (Figure 2D, Figure 2—figure supplement 5). Notably, we identified a threshold value of at least 0.25 mol% for efficient cell binding by qualitative confocal imaging as well as quantitative flow cytometry experiments (Figure 2D, Figure 2—figure supplement 5). Below this value, no uptake was observed, whereas above 0.25 mol% cellular binding was improved. Stoichiometric estimations assuming a bilayer thickness of 5 nm, a phosphatidylcholine headgroup area of 0.71 nm2 and an equal distribution of DSPE-PEG in the outer and inner nanoparticle membrane result in 157 ± 16, 79 ± 8, or 39 ± 4 maleimide moieties per liposome capable for lipopeptide conjugation corresponding to 0.5 mol%, 0.25 mol%, or 0.125 mol%, respectively (Maurer et al., 2001). Thus, a minimum of 80 functional maleimide moieties per nanoparticle is necessary for efficient cellular targeting after Myr-preS2-31 conjugation.

In vivo systemic circulation in the zebrafish vertebrate model

Since in vitro experimental models are not able to mimic the physiological complexity of nano-bio interactions at an organ level, we screened in the next step the effect of ligand density on pharmacokinetics of nanoparticles in vivo for Myr-preS2-48 and Myr-preS2-31 (Figure 3). Recently, we have reported that the zebrafish is a valuable pre-clinical tool to assess the systemic circulation and blood clearance of nanoparticulate drug delivery systems in vivo (Sieber et al., 2017; Campbell et al., 2018; Sieber et al., 2019b; Park, 2017; Yin et al., 2018; Sieber et al., 2019a).

Figure 3
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Systemic circulation of Myrcludex B-derived lipopeptide conjugated nanoparticles in vivo in the zebrafish model.

Nanoparticles were modified with different amounts of (A) Myr-preS2-48 or (B) short Myr-preS2-31 and injected into transgenic zebrafish embryos expressing green fluorescent protein in their vasculature endothelial cells (green signal). Membrane of nanoparticles was fluorescently labeled using DiI (red signal). Representative confocal laser scanning microscopy images of tail region 1 hpost injection.

https://doi.org/10.7554/eLife.42276.022

Thus, we injected DiI labeled nanoparticles modified with different amounts of targeting ligand (0.125 mol% - 1.0 mol%) into the duct of Cuvier of transgenic kdrl:EGFPs843 zebrafish embryos which express GFP in the vasculature endothelial cells. Already 1 h post injection, a clear qualitative difference in circulation characteristics of tested nanoparticles was detected. With increasing ligand density on the nanoparticle surface, the systemic circulation of nanoparticles decreased for both peptides (Figure 3) indicating that ligand modification of nanoparticles interferes with the shielding properties of PEG. Increased blood clearance was thereby paralleled by accumulation in the posterior caudal vein region. The observed binding pattern did not match a stabilin-2 scavenger receptor dependent nanoparticle clearance, which would be indicative for interactions with mammalian liver sinusoidal endothelial cells (LSECs) (Campbell et al., 2018). More likely a sequestration by macrophages is responsible for this clearance mechanism corresponding to an accumulation in the spleen of rodents (Sieber et al., 2019b).

Interestingly, nanoparticles modified with the shorter targeting peptide, that is Myr-preS2-31, showed increased systemic circulation (Figure 3B) as compared to Myr-preS2-48 modified nanoparticles (Figure 3A) at similar ligand densities. Thus, Myr-preS2-31 modified nanoparticles were selected for further investigations. However, nanoparticles modified with more than 0.5 mol% Myr-preS2-31 were as well excluded from further evaluation due to their poor systemic circulation and high clearance rate.

In vivo targeting ability in the zebrafish vertebrate model

In a next step, we investigated the targeting capacity of Myr-preS2-31 modified nanoparticles to human cells in vivo in the zebrafish model (Figure 4). In recent years, several groups have used xenografted zebrafish for various investigations including the assessment of nanoparticles (Sieber et al., 2019a; Evensen et al., 2016; Wertman et al., 2016; Brown et al., 2017; He et al., 2012; Lin et al., 2017; Veinotte et al., 2014; Wagner et al., 2010). Despite anatomical differences with mammals, zebrafish xenotransplantation models are an emerging preclinical tool offering several practical advantages as compared to mouse xenografting models including prolific reproduction, facilitated xenotransplantation (no immune rejection due to limited adaptive immune response), and optical transparency enabling high throughput screening. For our study, we used HEK293 cells stably expressing GFP for further genetic modification and establishment of xenotransplants (Witzigmann et al., 2015b). HEK293-GFP cells were transiently transfected with SLC10A1 to express the targeting factor for our hepatotropic nanoparticles. Wild type HEK293-GFP without SLC10A1 served as control. Both cell lines were injected into ABC/TU wild type zebrafish embryos to create human xenotranplants. The different nanoparticles were injected as soon as transgenic human cells stopped circulating and remained in the caudal vasculature tail region (i.e. after approximately 1 h). Interestingly, a clear difference in targeting capacity dependent on SLC10A1 expression and ligand density was revealed. Whereas there was no significant difference in targeting capacity at different ligand densities for SLC10A1-deficient HEK293-GFP cells (Figure 4A), a significant increase in binding to HEK293-GFP cells was observed if SLC10A1 was overexpressed as the nanoparticles could bind specifically and be readily internalized (Figure 4B). Most importantly, this was only valid for nanoparticles modified with 0.25 mol% Myr-preS2-31 (Figure 4, quantitative analysis). This illustrates that ligand density highly influences the balance between systemic circulation, systemic clearance rate and targeting efficiency of our liposome-based nanoparticles.

Figure 4 with 1 supplement see all
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Targeting ability of Myr-preS2-31 conjugated nanoparticles in vivo in xenotransplanted zebrafish embryos.

Nanoparticles were modified with different amounts of Myr-preS2-31 and injected into wild type zebrafish embryos xenotransplanted with human, GFP expressing HEK293 cells (green signal), (A) deficient or (B) expressing SLC10A1. Membrane of nanoparticles was fluorescently labeled using DiI (red signal). Yellow signals demonstrate colocalization (i.e. binding and internalization) of nanoparticles with HEK293-GFP cells. Representative brightfield and fluorescence images of tail region 1 h post injection are shown. Quantitative analysis of nanoparticle binding to HEK293-GFP cells is represented by Pearson´s Correlation Coefficient (PCC). All values are shown as box plots of biological replicates (n ≥ 2 independent experiments). *p<0.05. Numerical data for all graphs are shown in Figure 4—source data 1.

https://doi.org/10.7554/eLife.42276.023
Figure 4—source data 1

Targeting xenotransplanted cells in the zebrafish model.

https://doi.org/10.7554/eLife.42276.025

Nanoparticles modified with ligand densities below 0.25 mol% show a favorable systemic circulation but have an insufficient targeting ability. This also confirms our observations in vitro, where nanoparticles with a ligand density below 0.25 mol% did not significantly bind to HepG2 SLC10A1 cells. In sharp contrast, nanoparticles modified with higher Myr-preS2-31 targeting ligand densities (i.e. 0.5 mol%) have increased targeting ability in vitro. However, decreased systemic circulation and a high clearance rate under in vivo conditions counteract the advantage of higher ligand densities. Nanoparticles modified with 0.25 mol% Myr-preS2-31 have the highest targeting efficiency due to an ideal balance between target affinity and long circulation time in vivo. It should be noted that nanoparticles are internalized by target cells (Figure 4B) whereas free Myrcludex B apparently binds with high affinity to target cells but is not internalized (Figure 4—figure supplement 1). This phenomenon was recently observed by our team in rodents (data not shown) and was also reported from clinical trials in humans.

In vivo liver targeting of Myr-preS2-31 conjugated nanoparticles in mice

To elucidate the influence of ligand density on hepatotropism of our nanoparticles in vivo in mammals, we evaluated the pharmacokinetic properties of Myr-preS2-31 conjugated nanoparticles in mice. For this set of experiments, we used a dual labeling approach. The radioactive nuclide indium-111 (111In) was used for whole-body imaging and biodistribution studies whereas fluorescence labeling with DiI was used to evaluate intra-organ nanoparticle distribution. Importantly, we incorporated DTPA-conjugated DSPE into the lipid bilayer to chelate 111In on the surface of nanoparticles. This radiolabeling strategy has distinct advantages as compared to other labeling techniques or loading of 111In-oxine into nanoparticles (van der Geest et al., 2015). First, this radiolabeling method is robust, fast (within 45 min) and efficient with labeling efficiencies above 90%. Notably, free 111In was easily removed from nanoparticle formulations prior to injection using size exclusion chromatography (NAP-5 columns). Second, DTPA-DSPE enables retention of 111In in serum for at least 48 h at 37°C (>98% label retention) demonstrating the high stability necessary for in vivo studies of nanoparticulate drug delivery systems (van der Geest et al., 2015). Third, free 111In is rapidly eliminated via kidneys and excreted in the urine as shown previously (Harrington et al., 2000; Shih et al., 2017). This offers an easy assessment to differentiate between non-bound and nanoparticle bound 111In.

Four different lipid-based nanoparticles were prepared and injected intravenously into the tail vein of mice, that is PEGylated liposomes (negative control) and nanoparticles modified with 0.125 mol%, 0.25 mol% and 0.5 mol% Myr-preS2-31. Plasma and organs were harvested to perform a quantitative biodistribution analysis ex vivo 1 h post injection (Figure 5A). PEGylated nanoparticles showed the typical biodistribution of sterically stabilized nanoparticles with a strong signal in the blood (Figure 5A). Myr-preS2-31 conjugated liposomes demonstrated different biodistribution patterns depending on ligand density (Figure 5A). Modification of nanoparticles with 0.125 mol% Myr-preS2-31 did not alter the systemic circulation significantly (i.e. high blood pool signal). Only a minor increase in liver accumulation was observed as compared to ligand-lacking PEGylated nanoparticles (Figure 5A).

Figure 5 with 9 supplements see all
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In vivo biodistribution and liver targeting of Myr-preS2-31 conjugated nanoparticles in mice.

Nanoparticles were modified with different amounts of Myr-preS2-31 and labeled with radioactive 111In and fluorescent membrane dye (DiI, red signal). (A) Quantitative biodistribution studies were performed 1 h post injection. Radioactivity of each organ was determined with a γ-counter and the percentage of injected dose (%ID) per organ was calculated. B = blood, H = heart, Lu = lung, Li = liver, S = spleen, K = kidney. All values are shown as mean ± SD of biological replicates (n = 4 independent experiments). Numerical data for all graphs are shown in Figure 5—source data 1. (B) Fluorescence imaging (FI) of nanoparticles (DiI, red signal) in liver cryo-sections. Blue signal: Hoechst stain of cell nuclei. Scale bar = 100 µm. (C) Immunohistochemistry (IHC) of Myr-preS2-31 (red signal) in the liver sections 1 h after intravenous injection. Mice liver sections were stained with anti-Myr-preS2-31 antibody (MA18/7). Blue signals represent cell nuclei. Arrows indicate distinct localized accumulations.

https://doi.org/10.7554/eLife.42276.026
Figure 5—source data 1

Biodistribution in mice.

https://doi.org/10.7554/eLife.42276.036

Interestingly, nanoparticles modified with 0.25 mol% Myr-preS2-31 significantly enriched binding to the liver (Figure 5A). Further increase in ligand density (0.5 mol%) resulted in an increase in spleen accumulation, that is enhanced clearance by cells of the reticuloendothelial system (Figure 5A). Of note, none of the nanoparticle formulation resulted in an elimination via kidneys demonstrating the high stability and retention of the DTPA-DSPE chelated 111In.

Planar gamma scintigraphy imaging of injected mice and harvested organs at various time points (15 min and 60 min) confirmed these observations (Figure 5—figure supplements 1, 2 and 3). PEGylated nanoparticles demonstrated the typical systemic circulation with a strong signal in highly perfused organs, for example heart (Figure 5—figure supplements 1 and 2). Modification of nanoparticles with 0.25 mol% Myr-preS2-31 significantly increased the liver accumulation. Interestingly, further increase in Myr-preS2-31 modification (≥0.25 mol%) resulted in dominant location of radioactivity in an elongated structure in the far-left part of the abdomen under the liver, which was identified as the spleen (Figure 5—figure supplement 1). In order to confirm this observation, we injected mice with excessive Myr-preS2-31 modified nanoparticles (>0.5 mol%) and performed a planar imaging (Figure 5—figure supplement 3). Indeed, elevated Myr-preS2-31 modification resulted in an exclusive spleen accumulation, that is enhanced clearance by cells of the reticuloendothelial system. In order to exclude species specific effects, we also performed a planar gamma scintigraphy imaging of harvested organs from injected rats (Figure 5—figure supplement 4). Again, elevated Myr-preS2-31 modification has negative impacts on liver accumulation.

In order to highlight the ligand-density dependent hepatotropism, we calculated ratios between the blood pool and important organs, that is liver (i.e. target organ), spleen (i.e. clearance organ), and kidney (i.e. control organ since nanoparticle bound 111In should not show renal excretion) (Figure 5—figure supplement 5). Indeed, Myr-preS2-31 modification ≥0.25 mol% resulted in increased liver/spleen-to-blood ratios. Strikingly, nanoparticles modified with 0.25 mol% Myr-preS2-31 demonstrated a significant increase in the liver-to-kidney ratio confirming our conclusions from the zebrafish model, that 0.25 mol% Myr-preS2-31 is the optimal ligand density (Figure 4B).

The biodistribution studies were combined with fluorescence imaging of nanoparticle distribution (Figure 5B, Figure 5—figure supplement 6) and immunohistochemistry of Myr-preS2-31 distribution (Figure 5C, Figure 5—figure supplements 6–9) in liver, spleen, and kidney (i.e. nanoparticles and Myr-preS2-31 should not show renal excretion). PEGylated nanoparticles showed a weak fluorescent signal in the liver (Figure 5B). Importantly, these signals were not associated with the sinusoidal membrane of hepatocytes but arose from the high hepatic blood supply (Figure 5—figure supplement 8). No signals were observed in spleen and kidney (Figure 5—figure supplement 6). Modification of nanoparticles with 0.125 mol% Myr-preS2-31 did not result in significantly increased liver levels. A marginal binding of nanoparticles to hepatocyte membrane was visually observed (Figure 5B,C). This supports our hypothesis that a threshold level of targeting ligand density present on the nanoparticle surface is necessary for successful targeting. Importantly, strong signals for nanoparticles modified with 0.25 mol% Myr-preS2-31 were observed on the basolateral membrane of parenchymal liver cells (Figure 5B,C) demonstrating the strong hepatotropism of our nanoparticles. Further increasing the ligand density (i.e. 0.5 mol%) was detrimental and resulted in a diffuse hepatic staining pattern. Nanoparticles and their payload were detected as punctuated signals in the whole liver and did not show a specific membrane staining (Figure 5B, Figure 5—figure supplement 9). Myr-preS2-31 was detected in distinct localized areas only (Figure 5C). We conclude that nanoparticles modified with excessive Myr-preS2-31 densities (0.5 mol%) are rapidly cleared by liver resident macrophages, i.e. Kupffer cells. Subsequent re-distribution phenomena result in an unspecific nanoparticle signal in the whole liver.

Competition of NTCP-specific uptake into mouse hepatocytes in vivo

Since nanoparticles modified with 0.25 mol% Myr-preS2-31 allowed highly efficient liver targeting, we next investigated the NTCP specificity and the internalization process (Figure 6A). Therefore, we injected either labeled nanoparticles alone or together with free unlabeled Myrcludex B into mice (Figure 6B). Co-injection of Myrcludex B resulted in a clear decrease in liver enrichment by competitive inhibition of NTCP-binding as demonstrated by a change of signal.

Figure 6
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NTCP-specific uptake of Myr-preS2-31 conjugated nanoparticles into hepatocytes in vivo in mice.

(A) Schematic representation of NTCP-targeted nanoparticle binding to hepatocytes. Circulating nanoparticles pass the fenestrae of liver sinusoidal endothelial cells (LSEC) and subsequently bind to the NTCP in the basolateral membrane of hepatocytes facing the space of Disse. Prior to Myr-preS2-31 mediated NTCP binding, the myristoyl chain is inserted into the lipid bilayer. In close proximity to hepatocytes, acyl chain switches into cellular membrane due to high affinity of essential peptide sequence to NTCP binding site, thereby consolidating target transporter binding. (B) Nanoparticles were modified with 0.25 mol% of Myr-preS2-31 and labeled with radioactive 111In and fluorescent membrane dye (DiI, red signal). Planar imaging of mice 1 h post-injection. Competitive inhibition of liver binding by co-injection of free Myrcludex B clearly demonstrates NTCP-specific binding. Positions of liver and spleen are indicated by small circles. (C) Immunofluorescence staining of nanoparticles (red signal), targeting ligand (Myr-preS2-31, green signal, antibody staining), and Slc10a1 (cyan signal, antibody staining) in liver cryosections. Nuclei staining (blue signal) served as control for complete internalization; no overlap with Slc10a1. Scale bar = 20 µm. Colocalization analysis with Slc10a1 is represented by Pearson´s Correlation Coefficient (PCC). All values are shown as box plots of biological replicates (n = 3 independent experiments). *p<0.05. Numerical data for all graphs are shown in Figure 6—source data 1.

https://doi.org/10.7554/eLife.42276.037
Figure 6—source data 1

Internalization into hepatocytes.

https://doi.org/10.7554/eLife.42276.038

To reveal the localization of nanoparticles, we performed a confocal microscopy analysis of liver cryo-sections (Figure 6C). We stained liver cryo-sections using antibodies against Slc10a1 and Myr-preS2-31 (MA 18/7). Interestingly, nanoparticles that were internalized into parenchymal liver cells did not co-localize with Slc10a1 fluorescent signals. Myr-preS2-31 still colocalized with Slc10a1 suggesting that the targeting ligand was separated from the nanoparticle during cellular internalization as already observed in in vitro experiments. This phenomenon was confirmed by a colocalization analysis (Figure 6C). The observed cellular uptake is a surprising finding since HBV possesses pronounced host species specificity with regard to binding and infectivity. HBV binds to murine hepatocytes but cannot infect mice due to the lack of host cell dependency factors (Lempp et al., 2016). Therefore, chimeric mice transplanted with primary human hepatocytes have been developed to study anti-HBV drugs (Petersen et al., 2008; Lütgehetmann et al., 2012). In humans or chimpanzees only, HBV specifically binds to hepatocytes and subsequently infects the host.

Importantly, our NTCP-targeted nanoparticles apparently lack this species specificity. In contrast to HBV, our hepatotropic nanoparticles specifically bind to mouse hepatocytes in a Slc10a1-dependent manner and are subsequently internalized. The exact molecular interactions behind this internalization process will require additional studies to elucidate structural determinants important for cellular uptake and to better understand viral entry mechanisms, which are still unknown (Glebe and Urban, 2007).

Conclusions

In conclusion, the combination of in vitro investigations, the zebrafish model and in vivo experiments in rodents offered a unique approach to optimize our targeting ligand modified nanoparticles. The zebrafish model demonstrated to be an excellent tool to pre-screen various nanoparticle formulations, to assess the effect of Myrcludex B modifications on their pharmacokinetics and biodistribution, and thus increase the accuracy of predictions for experiments in rodents. The developed delivery systems can increase liver uptake levels, decrease accumulation in off-target tissues and at the same time avoid clearance by the reticuloendothelial system by mimicking HBV targeting properties. Despite the fact that current liver targeting strategies such as ASGPR- or LDLR-targeted delivery systems have already demonstrated improved drug and gene delivery in various preclinical models, these systems also suffer from certain drawbacks including complex synthesis of multivalent glycans or strong evidence that a majority of endocytosed gene carriers is recycled back to the cell exterior thereby reducing activity (Witzigmann et al., 2016a; Sahay et al., 2013). Due to the availability of efficient peptide manufacturing protocols, the proposed NTCP targeted delivery platform is an alternative and promising approach which warrants further investigation. For future clinical applications, optimized Myr-preS2-31 conjugated nanoparticles entrapping small molecule drugs, nucleic acids or proteins need to be studied in appropriate animal models of disease. In particular, we see a great potential for our nanoparticle targeting strategy in the field of metabolic diseases of the liver.

Materials and methods

Key resources table
Reagent type (species)
or resource		DesignationSource or referenceIdentifiersAdditional
information
Cell line (H. sapiens)HepG2 WTDOI: 10.1111/hepr.12599RRID:CVCL_0027Cell depository of the Institute of Pathology (University Hospital of Basel, Switzerland)
Cell line (H. sapiens)HepG2 SLC10A1DOI: 10.1053/j.gastro.2013.12.024RRID:CVCL_JY40Prof. Dr. Stephan Urban (University Hospital Heidelberg)
Cell line (H. sapiens)HuH7 WTDOI: 10.1111/hepr.12599RRID:CVCL_0336RIKEN Cell Bank (Ibaraki, Japan)
Cell line (H. sapiens)HuH7 SLC10A1DOI: 10.1053/j.gastro.2013.12.024Prof. Dr. Stephan Urban (University Hospital Heidelberg)
Cell line (H. sapiens)HeLa WT-RRID:CVCL_0030Prof. Dr. Jörg Huwyler (University of Basel)
Cell line (H. sapiens)HEK293-GFPDOI: 10.1021/acsami.5b01684Prof. Dr. Jörg Huwyler (University of Basel)
Cell line (Cricetulus griseus)CHODOI: 10.1021/bi702258zRRID:CVCL_0214Prof. Dr. Joachim Seelig (University of Basel)
Cell line (Cricetulus griseus)psgA745DOI: 10.1021/bi702258zProf. Dr. Joachim Seelig (University of Basel)
Genetic reagent (Danio rerio)kdrl:EGFPs843 zebrafishDOI: 10.1016/j.jconrel.2017.08.023https://zfin.org/ZDB-TGCONSTRCT-070117-47Prof. Dr. Markus Affolter (University of Basel)
Antibodyanti-Myr-preS2-31 antibody (MA18/7)--Prof. Dr. Wolfram Gerlich (Justus-Liebig-Universität Gießen); monoclonal human, 1:100 dilution
Antibodyanti-Slc10a1 (anti-Ntcp)--Prof. Bruno Stieger (University of Zurich); polyclonal rabbit, 1:100 dilution
Antibodyanti-FITC antibodyInvitrogen - ThermoFisher ScientificCatalog # 71–1900polyclonal rabbit, 1:100 dilution
SoftwareOriginPro 9.1 software-RRID:SCR_014212OriginLab Corporation
SoftwareFlowJo VX software-RRID:SCR_008520TreeStar
SoftwareImageJ Fiji-RRID:SCR_002285ImageJ

Synthesis of Myrcludex B-derived peptides

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Different peptides were synthesized by fluorenylmethoxycarbonyl/t-butyl (Fmoc/tBu) solid-phase synthesis using an Applied Biosystems 433A peptide synthesizer and modified with acyl chains as described previously (Schieck et al., 2013). Atto fluorescence dyes were either linked to the distal cysteine residue by maleimide chemistry or to the ε-amino group of an additionally introduced D-lysine at position two by NHS chemistry for mechanistic studies based on a triple fluorescence labeling strategy. In contrast to all other amino acids of Myrcludex B-derived lipopeptides, a D-amino acid was introduced in the latter case due to the chemical synthesis strategy used. Peptides were purified using preparative reverse-phase high performance liquid chromatography (HPLC, LaPrep P110, VWR International GmbH) with a Reprosil-Gold 120 C18 4 µm column (Dr. Maisch GmbH) and a variable gradient adapted to the peptides properties in a range of 100% H2O to 100% acetonitrile, both containing 0.1% TFA. Peptide identity was verified using an analytical Agilent 1100 HPLC system equipped with a Chromolith Performance RP-C18e column (Merck KGaA) coupled to a mass spectrometer (Exactive, Thermo Fisher Scientific).

Preparation of hepatotropic nanoparticles

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Hepatotropic nanoparticles based on liposomes were prepared using the film rehydration extrusion method as described previously (Detampel et al., 2014). The lipid membrane composition of nanoparticles consisted of DSPC (Lipoid AG), cholesterol (Sigma-Aldrich), DSPE-PEG2000 (Lipoid AG) at a molar ratio of 52.7:42.3:5. For the conjugation of HBV-derived peptides, DSPE-PEG2000 was replaced by DSPE-PEG2000-maleimide (Avanti Polar Lipids) at indicated molar ratios. For fluorescence labeling of lipid membrane, 1 mol% DiI (Thermo Fisher Scientific) was added to the lipid composition replacing DSPC. For radioactive labeling with 111In, DSPC was replaced by 3 mol% DSPE-DTPA (Avanti Polar Lipids). Desired ratios of lipids were mixed; a homogenous thin film was prepared and dried using a Rotavapor A-134 (Büchi). Lipid films were rehydrated using 0.01 M PBS pH 7.2 containing 1 mM EDTA (Sigma-Aldrich) to prevent metal ion catalyzed maleimide oxidation. For passive loading and fluorescence labeling of inner core, a 60 mM 5 (6)-carboxyfluorescein (Sigma-Aldrich) solution (pH 7.4) was used for the rehydration step. At this concentration >98% of the fluorescence is self-quenched (Figure 1—figure supplement 3). Resulting multilamellar vesicles were subjected to five freeze-thaw cycles and extruded 11 times through a polycarbonate membrane (Avanti Polar Lipids) with a pore size of 100 nm followed by 11 times through a polycarbonate membrane with a 50 nm pore size 10°C above transition temperature (i.e. 65°C for DSPC-based formulations). For functionalization with HBV-derived peptides, nanoparticles were mixed with peptides at molar maleimide-to-cysteine ratio of 1:1 and incubated at RT overnight. To remove non-conjugated peptides and/or free hydrophilic dye, size exclusion chromatography using a Sephadex G50 column (GE Healthcare) eluted with 0.01 M PBS pH 7.4 was performed. The size exclusion chromatography column was coupled to an UV detector to analyze recovery of nanoparticles based on peak areas. Hepatotropic nanoparticles were concentrated to a final lipid concentration of 10 mM using Amicon Ultra-4 centrifugal filter units with a 100 kDa molecular weight cut-off (Millipore). DiI and cholesterol were used as marker lipids to quantify total lipid content. DiI content was quantified based on relative fluorescence signals as compared to liposome standards and in combination with Triton X-100 treatment to account for potential DiI self-quenching. Samples were excited at 561 nm and fluorescence signals were recorded using a Spectramax M2 microplate reader (Molecular Devices). The cholesterol content was determined using the Cholesterol E cholesterol assay kit from Wako following the manufacturer’s protocol.

Loading of compounds into hepatotropic nanoparticles

FITC-peptide loading

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For passive loading of FITC-Ahx-yKKEEEK into nanoparticles, a 2 mg/mL FITC-peptide solution in a mixture of PBS/DMSO/EtOH at pH 7.0 was used for the rehydration step of the homogenous lipid film. Resulting multilamellar vesicles were processed as described in the Materials and methods section.

Propidium iodide loading

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For passive loading of propidium iodide into nanoparticles, a 10 mg/mL propidium iodide solution in PBS was used for the rehydration step of the homogenous lipid film. Resulting multilamellar vesicles were processed as described in the Materials and methods section including a final purification step.

Doxorubicin loading

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For loading of doxorubicin, an active drug loading strategy based on a citrate gradient was used as previously described (Mayer et al., 1990). The homogenous lipid film was rehydrated using a 300 mM citrate buffer at pH 4.0 and multilamellar vesicles were processed as described in the Materials and methods section. The pH of the external buffer solution was adjusted to pH 7.0 and nanoparticles were incubated with 2 mg/mL doxorubicin at 65°C for 15 min. Free doxorubicin was removed by size exclusion chromatography.

DNA vector loading

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Lipid nanoparticles entrapping DNA were prepared as previously described with modifications (Kulkarni et al., 2019; Kulkarni et al., 2018; Kulkarni et al., 2017). Briefly, lipids (ionizable lipid, cholesterol, DSPC, DSPE-PEG2000, and DSPE-PEG2000-Maleimide at a molar ratio of 50:39:10:0.75:0.25 mol%) were dissolved in ethanol at a total lipid concentration of 15 mM. The DNA vector was dissolved in 25 mM sodium acetate (pH 4.0) at an N/P ratio of 6. After T-junction mixing at a flow rate ratio of 3:1 v/v, the pH was neutralized using a 5x excess of D-PBS, the appropriate amount of Myr-preS2-31 was added, and the resulting suspension was dialyzed against D-PBS to remove residual ethanol.

Physicochemical characterization of hepatotropic nanoparticles

Dynamic light scattering

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Size and size distribution (polydispersity index, PDI) of nanoparticles were analyzed using a Delsa Nano C Particle Analyzer (Beckman Coulter) equipped with a 658 nm laser. Samples were measured in D-PBS at RT and a measurement angle of 165°. Data were converted using the CONTIN particle size distribution analysis (Delsa Nano V3.73/2.30, Beckman Coulter Inc).

Electrophoretic light scattering

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Zeta potential of nanoparticles was analyzed using a Delsa Nano C Particle Analyzer. Samples were measured in D-PBS at RT and a measurement angle of 15°. Data were converted using the Smoluchowski equation (Delsa Nano V3.73/2.30).

Transmission electron microscopy

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Size and morphology of nanoparticles were analyzed using transmission electron microscopy (TEM) as described previously (Witzigmann et al., 2015a). In brief, samples were deposited on a 400-mesh carbon-coated copper grid, negatively stained with 2% uranylacetate, and analyzed using a CM-100 electron microscope operating at 80 kV (Philips).

Fluorescence correlation spectroscopy

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Fluorescence correlation spectroscopy (FCS) analysis of nanoparticles was performed as described previously (Uhl et al., 2017). In brief, Atto488, Myr-preS2-48-Atto488 and Myr-preS2-48-Atto488 conjugated nanoparticles were analyzed using an inverted confocal fluorescence laser scanning microscope (Zeiss LSM 510-META/Confocor 2) equipped with a 40 × water immersion objective lens (Zeiss C-Apochromat 40×, numerical aperture 1.2). Fluorescence intensity fluctuations were measured for three independent samples and each measurement was repeated 20–30 times. Autocorrelation functions were fitted using a two-component model and diffusion times were calculated.

Cell culture

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Cell lines were purchased from ATCC or other recognized cell depositories (Institute of Pathology, University Hospital of Basel, Switzerland and RIKEN Cell Bank, Ibaraki, Japan) who perform authentication and quality-control tests on all distribution lots of cell lines (Witzigmann et al., 2016b). In addition, we performed authentication tests for all cell lines based on morphology check by microscope. All human cell lines were cultured at 37°C under 5% CO2 and saturated humidity in Dulbecco’s modified Eagle’s culture medium high glucose (DMEM, Sigma-Aldrich) supplemented with 10% fetal calf serum (Amimed), penicillin (100 units/mL, Sigma-Aldrich), and streptomycin (100 μg/mL, Sigma-Aldrich). Stable NTCP expressing liver derived cell lines, that is HepG2 SLC10A1 and HuH7 SLC10A1, were created by lentiviral transduction as published previously (Ni et al., 2014). For uptake experiments, different cell lines were seeded at a density of 2.5 × 104 cells/cm2 and allowed to adhere for 24 h. For confocal laser scanning microscopy experiments, cells were grown on poly-D-lysine (Sigma-Aldrich) coated glass cover slips (#1.5, Menzel) or well plates (TPP).

Transfection of cell lines

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For transient expression of the transporter, plasmids encoding for mNtcp (Slc10a1) or hNTCP (SLC10A1) were generated, amplifying the coding sequence from commercially obtained mRNA (Amsbio) by PCR. The following primers were used:

SLC10A1_for: 5′-ATGGAGGCCCACAACGCGTCT-3′,

SLC10A1_rev 5′-CTAGGCTGTGCAAGGGGA-3′;

Slc10a1_for 5`-GTGTTCACTGGGTCGGAGGATG-‘3,

Slc10a1_rev1 5`-CAGGTCCAGAGCAAATACTCATAGGAG-‘3.

Subsequently the amplicons were ligated into pEF6-V5/HIS (Invitrogen), followed by sequence verification (Microsynth). The resulting plasmids Slc10a1-pEF6 and SLC10A1-pEF6 and Lipofectamine 3000 (Sigma-Aldrich) were used for transfection of human cell lines. A standard transfection protocol was developed as follows: Plasmid DNA and P3000 reagent were diluted in Opti-MEM (Sigma-Aldrich) and rapidly mixed with Lipofectamine 3000 diluted Opti-MEM using a DNA-to-Lipofectamine 3000 w/V ratio of 3. After 5 min incubation, the transfection mix was added to adhered cells at a plasmid DNA concentration of 1 μg/mL. Control cells were either transfected with empty pEF6 vector or treated with Opti-MEM alone.

Assessment of cytocompatibility of nanoparticles

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To assess the cytocompatibility of nanoparticles modified with different Myrcludex B derived peptides a MTT cell viability assay was performed. Wild type HeLa cells, liver-derived wild type HepG2 cells and HepG2 SLC10A1 were seeded and cultured as described above. Nanoparticles were added to cells at final concentrations of 0.25 mM – 8 mM. After 24 h, MTT reagent (Sigma-Aldrich) was added to cells for 4 h. Formazan dye crystals were solubilized for 2 h using a mixture containing 3% (v/v) sodium dodecyl sulfate (Sigma-Aldrich) and 40 mM hydrochloric acid in isopropanol (Sigma-Aldrich). Absorption of reduced MTT and background signals was measured using a Spectramax M2 microplate reader at 570 nm and 670 nm, respectively. Control cells treated with buffer were used to calculate relative cell viability.

Uptake of nanoparticles in vitro

To assess the uptake rate and intracellular localization of nanoparticles, cell lines were incubated with different concentrations of nanoparticles at 37°C or 4°C. Nanoparticles were loaded with 5 (6)-carboxyfluorescein (payload) and/or incorporated DiI in their phospholipid-membrane. Myrcludex B derived peptides were fluorescently labeled if necessary as indicated above. At the indicated time points, confocal laser scanning microscopy or flow cytometry were used for qualitative and quantitative analysis, respectively.

Competitive inhibition experiments in vitro

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NTCP-specific uptake of nanoparticles was investigated by pre-incubation with 400 nM free Myrcludex B fluorescently labeled with Atto-565 or Atto-488 as indicated.

Binding mechanism studies in vitro

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The hepatic cell dependent binding mechanism of nanoparticles was investigated by pre-incubation with 300 µg/mL heparin sulfate.

Uptake mechanism studies on NTCP mediated internalization in vitro

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The uptake mechanism of nanoparticles into HepG2 SLC10A1 cells was investigated using different pharmacological pathway inhibitors as described previously (Lunov et al., 2011). Cells were pre-incubated using 100 µg/mL colchicine (micropinocytosis inhibitor), 10 µg/mL chlorpromazine (inhibitor of clathrin-mediated endocytosis), or 25 µg/mL nystatine (inhibitor of caveolin-mediated endocytosis) for 30 min before addition of nanoparticles.

Confocal laser scanning microscopy

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At indicated time points, cell nuclei were counterstained for 5 min using 1.0 μg/mL Hoechst 33342 (Sigma-Aldrich), washed with PBS and embedded using ProLong Gold antifading reagent (Invitrogen Life Technologies). For live cell imaging, cell nuclei were counterstained with Hoechst 33342, and if indicated cell membranes were stained with Cell Mask Deep Red Plasma Membrane Stain (1.0 μg/mL, Thermo Fisher Scientific) and NTCP was stained using fluorescently labeled Myrcludex B. Confocal laser scanning microscopy analysis was performed using an Olympus FV-1000 inverted microscope (Olympus Ltd.), equipped with a 60 × PlanApo N oil-immersion objective (numerical aperture 1.40).

Flow cytometry analysis

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To quantify the uptake rate of nanoparticles into non-hepatic and hepatic cell lines with different NTCP expression levels, flow cytometry analysis was performed. Cells were detached using 0.25% trypsin/EDTA (Sigma-Aldrich), washed twice with PBS and re-suspended in PBS containing 1% fetal calf serum, 0.05% NaN3, and 2.5 mM EDTA. At least 10,000 cells per setting were analyzed using a FACS Canto II flow cytometer (Becton Dickinson). Doublets were excluded and DiI or CF signals were measured. Relative mean fluorescence intensities (MFI) of DiI or CF signals normalized to untreated cells were calculated using Flow Jo VX software (TreeStar).

High-content screening

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To quantify the transfection of HepG2 cells deficient or expressing NTCP using DNA loaded nanoparticles, high-content screening was performed as described previously.(Lin et al., 2013) Cells were seeded in 96-well cell culture dishes, were allowed to adhere for 24 h, and treated with lipid nanoparticles at a DNA concentration of 1.5 μg/mL. To assess the transfection efficacy using high-content screening, cells were fixed with 3% paraformaldehyde 24 h post treatment and cell nuclei were counterstained with Hoechst 33342. Plates were scanned and analyzed using a Cellomics ArrayScan VTI (Thermo Scientific).

Zebrafish embryo culture

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Zebrafish embryos (Danio rerio) are a well-established vertebrate screening model for engineered nanomaterials (Campbell et al., 2018; Einfalt et al., 2018; Sieber et al., 2017). They were maintained in accordance with Swiss animal welfare regulations as described previously (Sieber et al., 2017). In brief, eggs from wild type ABC/TU and transgenic kdrl:EGFPs843 adult zebrafish were maintained in media at 28°C. Formation of pigment cells was prevented by 1-phenyl 2-thiourea (PTU, Sigma-Aldrich).

Injection of nanoparticles into zebrafish embryos

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To assess the systemic circulation of nanoparticles, samples were injected into transgenic kdrl:EGFPs843 zebrafish embryos (two dpf) as described previously (Sieber et al., 2017). In brief, calibrated volumes of 1 nL were injected into the duct of Cuvier of anesthetized and agarose-embedded zebrafish embryos using a micromanipulator (Wagner Instrumentenbau KG), a pneumatic Pico Pump PV830 (WPI), and a Leica S8APO microscope (Leica). The tail region of zebrafish embryos was imaged 1 h post injection (hpi) using an Olympus FV-1000 inverted confocal laser scanning microscope equipped with a 20 × UPlanSApo (numerical aperture 0.75) objective.

Targeting of xenotransplanted human cells in the zebrafish model

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Human HEK293 cells deficient or overexpressing SLC10A1 were detached from 6-well cell culture dishes using 1 mL pre-warmed DMEM, washed (5 min at 200 g) and resuspended in 10 µL DMEM. Human cells (3 nL) were injected into the duct of Cuvier of ABC/TU zebrafish embryos. As soon as transgenic human cells stopped circulating and remained in the caudal vasculature tail region (after approximately two hpi), nanoparticles (1 nL) were injected as described above. Brightfield and fluorescence images of the tail region were taken 1 hpi of nanoparticles.

Colocalization analysis. Binding of nanoparticles to HEK293 cells was analyzed using the JaCoP plug-in Fiji. Therefore, Pearson´s Correlation Coefficient (PCC) was determined to assess the extent of colocalization (Bolte and Cordelières, 2006).

Radioactive labeling of nanoparticles with 111In

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Labeling of nanoparticles with 111In was performed with modifications as described previously (van der Geest et al., 2015). Nanoparticles were prepared as described above in PBS at a total lipid concentration of 60 mM (including 3 mol% DSPE-DTPA). Size exclusion chromatography was used to exchange the buffer system to citrate buffered saline pH 5.4, fractions were pooled and finally concentrated using Amicon Ultra-4 centrifugal filter units (100 kDa size exclusion). Nanoparticles (30 µmol) were incubated with 40 µl of 111InCl3 (Mallinckrodt Pharmaceuticals) at 37°C for 45 min using a thermocycler. After incubation, 111In labeled nanoparticles were purified using NAP-5 columns (GE Healthcare) by elution with sterile saline (B. Braun Medical Inc). Fractions of 250 µL were collected and activity of each fraction was determined.

Planar imaging of mice in vivo

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All mice experiments were carried out in accordance with German legislation on animal welfare. Female NMRI mice (6–8 weeks) were obtained from Janvier Laboratories. For planar imaging, mice were anesthetized with Isoflurane (Baxter) and 111In labeled nanoparticles with a total activity of 8–10 MBq (corresponding to 100 µL) were intravenously injected into the tail vein. Afterwards, the animals were placed in prone position (see Figure 5—figure supplements 2A and 3A) on a planar gamma-imager (Biospace) equipped with a high energy collimator as described previously (Müller et al., 2013; Wischnjow et al., 2016). Images were recorded at the indicated time points with 10 min acquisition time.

Planar imaging of harvested organs from mice and rats ex vivo

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For planar imaging of organs, animals were anesthetized with Isoflurane (Baxter) and 111In labeled nanoparticles were intravenously injected into the tail vein. Animals were sacrificed 15 min or 1 h post injection, organs were harvested and placed on a planar gamma-imager (Biospace) equipped with a high energy collimator. Images were recorded at the indicated time points with 10 min acquisition time.

Quantitative organ biodistribution of nanoparticles in mice ex vivo

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For biodistribution studies, 111In labeled nanoparticles with a total activity of 1–2 MBq (corresponding to 100 µL) were intravenously injected into the tail vein of wild type mice. Animals were sacrificed (n = 3 per nanoparticle administration) 1 h post injection, organs were harvested and the radioactivity in each organ was measured with a Berthold LB 951G gamma counter. Each organ-associated activity was related to the injected dose. The percentage of injected dose (%ID) per organ was calculated using standard values for organ weights (Mühlfeld et al., 2003).

Fluorescence imaging of nanoparticles in tissue cryo-sections

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Nanoparticles incorporating 1 mol% DiI were intravenously injected into the tail vein of wildtype mice. Animals were sacrificed 1 h post injection and organs were snap-frozen in liquid nitrogen. Cryo-sections of 16 µm were mounted on Superfrost Plus Ultra microscope slides (Thermo Fisher Scientific) and counterstained with Hoechst 33342 (2 µg/mL). Slides were embedded in Prolong Gold Antifade Mountant (Thermo Fisher Scientific), sealed with nail polisher and analyzed using an Olympus FV-1000 inverted confocal laser scanning microscope equipped with a 40x UPlanFL N oil-immersion objective (numerical aperture 1.30).

Immunohistochemistry of targeting ligand in tissue sections

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After intravenous tail vein injection of nanoparticles, the mice were euthanized, organs were harvested, rinsed with PBS and immediately placed in a 4% formaldehyde solution in PBS. After fixation for 24 h, organs were dehydrated and embedded in paraffin. Sections of 5 µm thicknesses were cut using a microtome MICROM HM 355, placed onto a microscope slide and dried at 37°C. After dewaxing and rehydration, epitope retrieval was performed. The primary antibody against Myr-preS2-31 (MA18/7, kind gift from Wolfram Gerlich) was added overnight at 4°C, before incubation with the secondary antibody. Finally, slides were counterstained with hemalum (Merck KGaA) for 10 min, blued with tap water and mounted using Aquatex (Merck Millipore).

Immunofluorescence imaging of liver cryo-sections

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Animals were sacrificed 3 h post injection of nanoparticles and liver cryo-sections (16 µm) were prepared as described above. Slides were stained using primary antibodies against Myr-preS2-31 (MA18/7, 1:100 dilution) and Slc10a1 (provided by Prof. Bruno Stieger, University Zürich, 1:100 dilution). Finally, cell nuclei were counterstained with Hoechst 33342 (2 µg/mL) and analyzed by confocal microscopy as described above.

Statistical analysis

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Statistical analysis for all experiments was performed by one-way analysis of variance (ANOVA) followed by Bonferroni post-hoc test using OriginPro 9.1 software (OriginLab Corporation). Differences between groups were considered to be statistically significant at the indicated p-values.

Data availability

All data generated or analysed during this study are included in the manuscript and supporting files. Numerical data for all quantitative graphs are provided in the Figure source data.

References

    1. Braet F
    2. Wisse E
    (2002)
    Structural and functional aspects of liver sinusoidal endothelial cell fenestrae: a review
    Comparative Hepatology 1:.

Decision letter

  1. Bavesh D Kana
    Reviewing Editor; University of the Witwatersrand, South Africa
  2. Didier Y Stainier
    Senior Editor; Max Planck Institute for Heart and Lung Research, Germany
  3. Sjoerd Hak
    Reviewer

In the interests of transparency, eLife includes the editorial decision letter and accompanying author responses. A lightly edited version of the letter sent to the authors after peer review is shown, indicating the most substantive concerns; minor comments are not usually included.

[Editors’ note: this article was originally rejected after discussions between the reviewers, but the authors were invited to resubmit after an appeal against the decision.]

Thank you for submitting your work entitled "Optimization-by-Design of a Hepatotropic Hepatitis B Virus-Mimetic Nanocarrier" for consideration by eLife. Your article has been reviewed by two peer reviewers, and the evaluation has been overseen by a Reviewing Editor and a Senior Editor. The following individuals involved in review of your submission have agreed to reveal their identity: Sjoerd Hak (Reviewer #2).

Our decision has been reached after consultation between the reviewers. Based on these discussions and the individual reviews below, we regret to inform you that your work will not be considered further for publication in eLife.

Your study reports a novel advance, using interesting methodologies. However, there are numerous concerns, specifically regarding experiments in animal models that preclude further consideration for publication. Also the applicability of the approach is somewhat overstated and not supported by the data presented.

Reviewer #1:

The manuscripts entitled 'Optimization-by-Design of a Hepatotropic Hepatitis B Virus-Mimetic Nanocarrier' describes investigations aimed at developing use of a myristolated preS peptide sequence derived from HBV to target liposomes to hepatocytes. Several experiments were carried out, which entailed analysis in cultured cells, zebrafish and mice. Although interesting, the work has significant shortcomings and is not suitable for publication in its present form. Some of the major concerns are the following:

1) Throughout the manuscript the nanoparticle is referred to as a 'virus mimetic'. However, the only similarity of the liposome to a virus is presence of the HBV-derived peptide. The description therefore seems to overstate the virus like properties. The particle does not have a capsid, nor does it carry any nucleic acid. Both are essential features of viruses.

2) Limitations of vectors used for delivery of nucleic acids are provided as justification for developing the liver targeting liposome. This point is re-emphasized in the conclusions where it is stated that the vector may have utility for treatment of monogenic diseases. However this opinion is not supported by the content of the manuscript. None of the experimentation characterizes properties of the vector when complexed to nucleic acids, nor is there any comparison to lipoplexes that use other targeting moieties, such as galactose.

3) In the experiments carried out on cultured cells, evidence that the payload is active or reaches the cytosol is not convincing. The punctate nature of the fluorescence suggests that the molecules may be trapped in the endosomes (Figure 1C).

4) Utility of the zebrafish model is minimal and the manuscript overstates the importance of the results from these experiments.

5) Data from analysis of the biodistribution of the particles and the radioactive payload in mice are particularly problematic.

a) Figure 6B indicates a thoracic location of the liver. Also images of mice in Figures 5 and 6 show dominant location of radioactivity in bilobed structures that look remarkably like lungs.

b) It is not clear whether the mice are prone or supine, which means that the left or right sides of the animals is unclear. Organ location is thus uncertain, and this adds to concerns about interpretation of the data

c) Evidence that the 111In was retained inside the nanoparticles is lacking. If the radioactivity diffused out of the particles images of the animals could reflect distribution of uncomplexed radioactivity.

Reviewer #2:

This study describes the development of liposomes conjugated with hepatitis B virus-derived peptides, which bind to the sodium-taurocholate co-transporting polypeptide (NTCP) on hepatocytes. Different forms of the peptide as well as densities of selected peptides were optimized in vitro with respect to NTCP binding, and in vivo in both zebrafish and mice with respect to pharmacokinetics and hepatocyte targeting.

I consider this a comprehensive study and the build-up of the manuscript is logical. The integrated use of the zebrafish model is appealing and it seems a useful tool in nanoparticle optimization studies. Overall, the study is well-done and is suitable for publication in eLife. I have one major issue, which relates to the data presented in Figure 5:

Animals were sacrificed 1 h post injection at which the blood pool levels varied significantly for the different formulations tested. Furthermore, the images reported in Figure 5D indicate very similar distributions in the liver of the 0.125 and 0.25 mol% formulations. Since differences in circulation time will affect targeting levels, the 0.125 mol% formulation may exhibit high liver targeting as well? Reporting ROI analysis of the in vivo images as well as ratios between for example blood/spleen/liver may be useful here.

[Editors’ note: what now follows is the decision letter after the authors submitted for further consideration.]

Thank you for sending your article entitled "Optimization-by-Design of a Hepatotropic Hepatitis B Virus-Mimetic Nanocarrier" for peer review at eLife. Your article is being evaluated by three peer reviewers, and the evaluation is being overseen by a Reviewing Editor and Didier Stainier as the Senior Editor.

Given the list of essential revisions, including new experiments, the editors and reviewers invite you to respond within the next two weeks with an action plan and timetable for the completion of the additional work. We plan to share your responses with the reviewers and then issue a binding recommendation.

1) Although the authors mentioned small molecule drugs, nucleic acids or proteins can be encapsulated and studied in appropriate disease models in the future. Lake of demonstration of further application may hamper the impact of this work. The authors should show the application of the carriers, which is a usual practice for high impact journals such as eLife. For example, does the liver-specific carrier increases plasmid DNA delivery and enhanced the transfection efficacy in livers sites?

2) The fact that ASGPR-targeted delivery systems can improve gene/drug delivery has been already well studied. Although the authors defined their drug carriers as alternative approaches. The advantage and limitation of the alternative approaches should be highlighted and discussed.

3) The anatomical data and their interpretation continue to be problematic. Shifting the outline of the animal(s) in the revised manuscript to align radioactivity with expected organ distribution is questionable and raises doubts about reliability of the data. Also, the location of the radioactivity does not correlate with murine anatomy and definition of organ structures. The spleen is shown as a lower abdominal organ, which is far removed from the liver on the transverse plane. This is not correct. Although information about imaging the mice in the prone position is now included, the images are presented unconventionally. Left and right sides, not indicated, are inverted. This issue has persisted. Please attempt to address it effectively. Perhaps consider conducting the imaging again and provide pictures if multiple animals – with multiple views.

4) Xenografted zebrafish are not widely employed in the field of vectorology, and arguments about the usefulness of the model are not compelling. You have to revise your text accordingly.

Reviewer #1:

Concerns about the manuscript remain in the revised version. The following are particular issues.

The anatomical data and their interpretation continue to be problematic. Shifting the outline of the animal(s) in the revised manuscript to align radioactivity with expected organ distribution is questionable and raises doubts about reliability of the data. Also, the location of the radioactivity does not correlate with murine anatomy and definition of organ structures. The spleen is shown as a lower abdominal organ, which is far removed from the liver on the transverse plane. This is not correct. Although information about imaging the mice in the prone position is now included, the images are presented unconventionally. Left and right sides, not indicated, are inverted.

Xenografted zebrafish are not widely employed in the field of vectorology, and arguments about the usefulness of the model are not compelling.

Reviewer #2:

All major concerns have been addressed satisfactory.

The demonstration of successful intracellular delivery of active nanoparticle payload (Figure 1—figure supplement 7 and 8) is not very convincing, the conclusion is based on images of 20 cells at most.

Although these images (Figure 1—figure supplement 7 and 8) indeed support the conclusion, more convincing results can be relatively easily obtained with very standard assays. However, taking the complete manuscript and focus of the study into account, I consider the manuscript complete, relevant, and suitable for publication in eLife.

Reviewer #3:

This is an interesting study about the use of HBV targeting properties to achieve liver-specific delivery. The authors developed a potent liver-specific drug delivery carrier modified with an alternative liver-targeting moiety. They utilized the zebrafish and murine model to optimize and characterize the ligand-modified liposome. The liver-specific delivery carrier showed increased liver uptake and decreased off-target delivery to other tissues in murine models. In general, the article describes a well performed study. There are some major concerns:

1) Although the authors mentioned small molecule drugs, nucleic acids or proteins can be encapsulated and studied in appropriate disease models in the future. Lake of demonstration of further application may hamper the impact of this work. The authors should show the application of the carriers, which is a usual practice for high impact journals such as eLife. For example, does the liver-specific carrier increases plasmid DNA delivery and enhanced the transfection efficacy in livers sites?

2) The fact that ASGPR-targeted delivery systems can improve gene/drug delivery has been already well studied. Although the authors defined their drug carriers as alternative approaches. The advantage and limitation of the alternative approaches should be highlighted and discussed.

https://doi.org/10.7554/eLife.42276.041

Author response

[Editors’ note: the author responses to the first round of peer review follow.]

The rejection of our manuscript based on reviewer #2 is disappointing to us as the comments mainly criticized the term “virus-mimetic” and the mention of nucleic acid delivery as a future perspective. It is our opinion that both points addressed by the reviewer are not related to the quality or value of our experimental work but are in principle a matter of emphasis of the manuscript. The points addressed by reviewer #2 were now corrected in order to clarify the scope of our manuscript. In brief, we added new experiments, provide additional references, and rewrote the manuscript accordingly.

In addition, we feel that reviewer #2 did not take into account critical information already presented in our manuscript. We would like to point out that some of the concerns of the reviewer were already addressed based on presented data (Figure 1—figure supplement 6 and Figure 5B). These paragraphs were now rewritten to address the shortcomings highlighted by reviewer #2. Finally, we regret that recent headlines about research using the zebrafish as an early vertebrate in vivo model for nanoparticle screening became available during the review process only. We are convinced that this information would alleviate concerns of reviewer #2 related to the validity of our model and our present work was referenced accordingly. Based on the above points, we feel a strong need to contact you again. Considering the scope of your journal, our work would be of great interest for readers of eLife.

As discussed, we have directly addressed all reviewer comments, especially the concerns of reviewer #1.

Reviewer #1:

The manuscripts entitled 'Optimization-by-Design of a Hepatotropic Hepatitis B Virus-Mimetic Nanocarrier' describes investigations aimed at developing use of a myristolated preS peptide sequence derived from HBV to target liposomes to hepatocytes. Several experiments were carried out, which entailed analysis in cultured cells, zebrafish and mice. Although interesting, the work has significant shortcomings and is not suitable for publication in its present form. Some of the major concerns are the following:

1) Throughout the manuscript the nanoparticle is referred to as a 'virus mimetic'. However, the only similarity of the liposome to a virus is presence of the HBV-derived peptide. The description therefore seems to overstate the virus like properties. The particle does not have a capsid, nor does it carry any nucleic acid. Both are essential features of viruses.

We thank the reviewer for raising this concern. As the reviewer suggested, we modified the manuscript including title and figures. We replaced the term “virus-mimetic” throughout the manuscript with “nanoparticle” or variations such as “NTCP-targeted nanoparticles”. The “Title” was updated as follows:

Title: “Optimization-by-Design of Hepatotropic Lipid Nanoparticles Targeting the Sodium-Taurocholate Cotransporting Polypeptide”

2) Limitations of vectors used for delivery of nucleic acids are provided as justification for developing the liver targeting liposome. This point is re-emphasized in the conclusions where it is stated that the vector may have utility for treatment of monogenic diseases. However this opinion is not supported by the content of the manuscript. None of the experimentation characterizes properties of the vector when complexed to nucleic acids, nor is there any comparison to lipoplexes that use other targeting moieties, such as galactose.

We thank the reviewer for this comment. The major scope of this study was the development and in-depth optimization of NTCP-targeted nanoparticles using a unique approach of combining in vitroinvestigations and experiments in rodents with the emerging zebrafish model. Since the reviewer’s concern is not related to the validity of our study, we deleted statements regarding the delivery of nucleic acids and modified the “Introduction” and “Conclusion” section as follows:

Introduction: “In particular for the cell-type specific delivery of macromolecular therapeutic agents, selective targeting of parenchymal liver cells and internalization is needed.” AND “However, studies investigating alternative targeting strategies based on other hepatocyte-specific receptors are limited.”

Conclusion: “In particular, we see a great potential for our nanoparticle targeting strategy in the field ofmetabolic diseases of the liver.”

3) In the experiments carried out on cultured cells, evidence that the payload is active or reaches the cytosol is not convincing. The punctate nature of the fluorescence suggests that the molecules may be trapped in the endosomes (Figure 1C).

The comment of the reviewer, that there is no evidence that the payload is active or reaches the cytosol, ignores data presented in the Supplementary Information (Figure 1—figure supplement 8). We demonstrate the time-dependent internalization and toxicity of doxorubicin loaded nanoparticles into hNTCP overexpressing HepG2 cells. This result demonstrates that the payload is released into the cytosol resulting in cytotoxic effects. To avoid such misunderstanding, we emphasized this experiment as follows:

Results and Discussion: “Interestingly, Myr-preS2-31 modification enhanced the cytotoxic effects of propidium iodide and doxorubicin as compared to PEGylated nanoparticles (Figure 1—figure supplement 7 and 8) demonstrating that the payload is active and reaches the cytosol.”

In addition, we included an additional study performed using propidium iodide loaded nanoparticles. This data set confirms the release of the payload inside the cells resulting in nuclear accumulation of propidium iodide. An additional Figure (Figure 1—figure supplement 7) is presented. The manuscript was modified as follows:

Results and Discussion: “Of note, propidium iodide is a cell membrane impermeable drug. Thus, NTCP- targeted nanoparticles enabled internalization into cells and successful release into cytosol indicated by enhanced cytotoxic effects and nuclear counterstain.”

Legend Figure 1—figure supplement 7: “Time-dependent internalization and toxicity of propidium iodide loaded nanoparticles into hNTCP overexpressing HepG2 cells. Nanoparticles were passively loaded with propidium iodide (red signal). Representative confocal laser images for PEG nanoparticles and Myr-preS2-31 modified nanoparticles after specific time points are shown. Scale bar = 20 µm.”

Materials and methods: “Propidium iodide loading. For passive loading of propidium iodide into nanoparticles, a 10 mg/mL propidium iodide solution in PBS was used for the rehydration step of the homogenous lipid film. Resulting multilamellar vesicles were processed as described in the Materials and methods section including a final purification step.”

4) Utility of the zebrafish model is minimal and the manuscript overstates the importance of the results from these experiments.

We thank the reviewer for the critical comment indicating us that we did not highlight enough the breakthrough of this study in respect to state-of-the-art. In addition, we regret that recent headlines about our research using the zebrafish as an early vertebrate in vivomodel for nanoparticle screening became available during the review process only. The zebrafish has emerged as an early vertebrate in vivomodel for nanoparticle screening and our recent publications have been highlighted in several top-tier journals including ACS Nano and Journal of Controlled Release. In addition, we have an accepted original article in Nanomedicine:NBM and a review article in Advanced Drug Delivery Reviews. References were added accordingly. Recently, Shan et al. (doi: 10.1007/s13346-014-0210-2) reported huge discrepancies between in vitrosystems and rodent experiments during the development of targeted nanomedicines. Thus, there is a tremendous need to find innovative strategies for the development of cell-type specific delivery systems. It is important to mention, that the zebrafish model was not used as an alternative to rodent experiments but as a complementary in vivomodel to screen our nanocarriers. The zebrafish offers unique advantages: i) high reproducibility, ii) low costs, iii) high level of genetic homology to humans, iv) availability of transgenic lines, and v) most importantly optical transparency. This enables in vivoimaging at spatio-temporal resolution (i.e. down to a cellular level and at various time points). Consequently, we combined transgenic zebrafish lines with fluorescently labeled nanocarriers. Our approach offers the possibility to gain advanced insights into the circulation behavior and targeting properties of nanocarriers. We validated the data obtained in the zebrafish model in an established rodent model. To highlight the value of our work, that, we provide an additional reference and modified the “Introduction” and “Conclusion” sections as follows:

Introduction: “Recently, Shan et al. reported huge discrepancies between in vitro systems and rodent experiments during the development of targeted nanomedicines.(Shan et al., 2015) Therefore, we used the zebrafish as a complementary in vivo screening model based on our previous work. (Sieber et al., 2018; Campbell et al., 2018; Einfalt et al., 2018; Sieber et al., 2017) We assessed the effect of nanoparticles` ligand type and ligand density on their pharmacokinetics.” and “Strikingly, nanoparticles modified with 0.25 mol% Myr preS2 31 demonstrated a significant increase in the liver-to-kidney ratio confirming our conclusions from the zebrafish model, i.e. 0.25 mol% Myr-preS2-31 as an optimal ligand density (Figure 4B).”

Conclusions: “…and thus increase the accuracy of predictions for experiments in rodents”

5) Data from analysis of the biodistribution of the particles and the radioactive payload in mice are particularly problematic.

a) Figure 6B indicates a thoracic location of the liver. Also images of mice in Figures 5 and 6 show dominant location of radioactivity in bilobed structures that look remarkably like lungs.

b) It is not clear whether the mice are prone or supine, which means that the left or right sides of the animals is unclear. Organ location is thus uncertain, and this adds to concerns about interpretation of the data

c) Evidence that the 111In was retained inside the nanoparticles is lacking. If the radioactivity diffused out of the particles images of the animals could reflect distribution of uncomplexed radioactivity.

We thank the reviewer for these comments regarding the biodistribution analysis.

a) This is a very important notion. We had the possibility to discuss this issue with experts in the field. Indeed, the presented qualitative data allows different interpretation. The dominant location of radioactivity in a bilobed structure in the abdominal cavity with an enhanced intensity in the right lobe suggesting the liver. Lungs would be expected to be symmetrical and localized in the thorax; see whole-body mouse atlas for comparison of organ localization (Baiker et al., 2008). In addition, quantitative biodistribution studies of harvested organs demonstrate that there is no accumulation in the lung. However, to clarify this point, we restrict our discussion to the quantitative biodistribution analysis. The planar imaging will just be used for informative purposes (now Figure 5—figure supplement 2). We adjusted Figure 5 and 6 accordingly and modified the manuscript as follows:

Results and Discussion: “One-hour post injection, plasma and organs were harvested to perform a quantitative biodistribution analysis ex vivo (Figure 5A). PEGylated nanoparticles showed the typical biodistribution of sterically stabilized nanoparticles with a strong signal in the blood (Figure 5A). […] Planar γ scintigraphy imaging of injected mice confirmed these observations (Figure 5—figure supplement 2).”

Legend Figure 5—figure supplement 2: “in vivo biodistribution and liver targeting of Myr-preS2-31 conjugated nanoparticles in mice. Nanoparticles were modified with different amounts of Myr-preS2-31. Static planar imaging of mice 15 min after intravenous injection of different 111In labeled nanoparticles with approximately 8 MBq.”

b) We included the position of the mice, provide an additional reference and modified the “Materials and methods” section as follows:

Materials and methods: “Afterwards, the animals were placed in prone position on a planar gamma-imager (Biospace) equipped with a high energy collimator as described previously.(Müller et al., 2013; Wischnjow et al., 2016)”

c) This comment of the reviewer ignores several aspects already presented in the manuscript, e.g. that 111In was never encapsulated inside the nanoparticles. Instead we used a lipid-chelator (i.e. DSPE-DTPA) to label the nanoparticle surface with 111In. In order to clarify this comment, we included a Discussion section highlighting the advantages of our labeling strategy. Two additional references are provided and the manuscript was modified as follows:

Results and Discussion: “Importantly, we incorporated DTPA-conjugated DSPE into the lipid bilayer to chelate 111In on the surface of nanoparticles. […] This offers an easy assessment to differentiate between non bound and nanoparticle bound 111In.

Reviewer #2:

This study describes the development of liposomes conjugated with hepatitis B virus-derived peptides, which bind to the sodium-taurocholate co-transporting polypeptide (NTCP) on hepatocytes. Different forms of the peptide as well as densities of selected peptides were optimized in vitro with respect to NTCP binding, and in vivo in both zebrafish and mice with respect to pharmacokinetics and hepatocyte targeting.

I consider this a comprehensive study and the build-up of the manuscript is logical. The integrated use of the zebrafish model is appealing and it seems a useful tool in nanoparticle optimization studies. Overall, the study is well-done and is suitable for publication in eLife. I have one major issue, which relates to the data presented in Figure 5:

Animals were sacrificed 1 hour post injection at which the blood pool levels varied significantly for the different formulations tested. Furthermore, the images reported in Figure 5D indicate very similar distributions in the liver of the 0.125 and 0.25 mol% formulations. Since differences in circulation time will affect targeting levels, the 0.125 mol% formulation may exhibit high liver targeting as well? Reporting ROI analysis of the in vivo images as well as ratios between for example blood/spleen/liver may be useful here.

We thank the reviewer for this important suggestion. We calculated ratios between the blood pool levels and the three most important organs, i.e. liver (i.e. target organ), spleen (i.e. clearance organ), and kidney (i.e. control organ since nanoparticle bound 111In should not show renal excretion). An additional Figure (Figure 5—figure supplement 1) is presented and the manuscript was modified as follows:

Results and Discussion: “In order to highlight the ligand-density dependent hepatotropism, we calculated ratios between the blood pool and important organs, i.e. liver (i.e. target organ), spleen (i.e. clearance organ), and kidney (i.e. control organ since nanoparticle bound 111In should not show renal excretion) (Figure 5—figure supplement 1). Indeed, Myr preS2-31 modification ≥ 0.25 mol% resulted in increased liver/spleen-to-blood ratios.”

Legend Figure 5—figure supplement 1: “Organ ratios of ex vivo biodistribution analysis. Nanoparticles were modified with different amounts of Myr-preS2-31 and labeled with radioactive 111In. Quantitative biodistribution studies were performed 1 hour post injection. Radioactivity of each organ was determined with a γ-counter. Ratios of injected dose (%ID) per organ between the blood pool level and selected organs, i.e. liver (i.e. target organ), spleen (i.e. clearance organ), and kidney (i.e. control organ since nanoparticle bound 111In should not show renal excretion) were calculated. All values are shown as box plots of biological replicates (n = 3 independent experiments). *p < 0.05, **p < 0.01, ***p < 0.001.”

[Editors' note: the authors’ plan for revisions was approved and the authors made a formal revised submission.]

Reviewer #1:

Concerns about the manuscript remain in the revised version. The following are particular issues.

The anatomical data and their interpretation continue to be problematic. Shifting the outline of the animal(s) in the revised manuscript to align radioactivity with expected organ distribution is questionable and raises doubts about reliability of the data. Also, the location of the radioactivity does not correlate with murine anatomy and definition of organ structures. The spleen is shown as a lower abdominal organ, which is far removed from the liver on the transverse plane. This is not correct. Although information about imaging the mice in the prone position is now included, the images are presented unconventionally. Left and right sides, not indicated, are inverted.

The quantitative biodistribution studies of harvested organs demonstrated that nanoparticles modified with 0.25 mol% Myr-preS2-31 allowed highly efficient liver targeting while further increase in Myr-preS2-31 modification resulted in enhanced clearance by the spleen. In order to confirm this observation, we performed additional experiments in mice and rats. We injected 111In labeled nanoparticles and performed a planar γ scintigraphy analysis in vivo of the whole body and ex vivo of harvested organs. Photographical pictures were taken to indicate position and organ type. Rats were selected as additional species to increase the value of our study and to exclude species dependent effects. Three additional figures are provided (Figure 5—figure supplement 2-4), additional methods were added, and the manuscript was updated as follows:

Materials and methods: “Planar imaging of harvested organs from mice and rats ex vivo. For planar imaging of organs, animals were anesthetized with Isoflurane (Baxter) and 111In labeled nanoparticles were intravenously injected into the tail vein. Animals were sacrificed 15 min or 1 hour post injection, organs were harvested and placed on a planar gamma-imager (Biospace) equipped with a high energy collimator. Images were recorded at the indicated time points with 10 min acquisition time.”

Results and Discussion: “Planar gamma scintigraphy imaging of injected mice and harvested organs at various time points (15 min and 60 min) confirmed these observations (Figure 5—figure supplement 1, 2 and 3). […] Again, elevated Myr-preS2-31 modification has negative impacts on liver accumulation.”

Figure 5—figure supplement 1: “…Increase in Myr-preS2-31 modification (≥ 0.25 mol%) resulted in dominant location of radioactivity in a bilobed structure in the abdominal cavity with an enhanced intensity in the right lobe indicating the liver. In addition, nanoparticles with increased Myr-preS2-31 modification accumulated in an elongated structure in the far-left part of the abdomen under the liver, which is the spleen. For tissue identification and signal quantification see Figure 5A and Figure 5—figure supplement 2 and 3).”

Figure 5—figure supplement 2: “in vivo biodistribution and ex vivo organ distribution of PEGylated nanoparticles in mice. (A) Static planar imaging of mice in prone position 15 min after intravenous injection of different 111In labeled nanoparticles. Planar ex vivo imaging of harvested organs from mice (B) 15 min and (C) 60 min post injection.”

Figure 5—figure supplement 3: “in vivo biodistribution and ex vivo organ distribution of nanoparticles with elevated Myr-preS2-31 modification. (A) Static planar imaging of mice in prone position 15 min after intravenous injection of different 111In labeled nanoparticles. Planar ex vivo imaging of harvested organs from mice (B) 15 min and (C) 60 min post injection.”

Figure 5—figure supplement 4: “Organ biodistribution of different nanoparticles in rats. Planar ex vivo imaging of harvested organs from rats injected with (A) PEGylated nanoparticles or (B) nanoparticles with elevated Myr-preS2-31 modification was performed 60 min post injection.”

Xenografted zebrafish are not widely employed in the field of vectorology, and arguments about the usefulness of the model are not compelling.

We agree with the reviewer that zebrafish are not yet widely employed in the field of vectorology. In the present work, we therefore combine results in the zebrafish with data from two additional species (mouse and rat). Furthermore, we would like to point out that zebrafish is an emerging screening model for nanomedicines. This is increasingly recognized by other experts in the field. Our recent published review article “Zebrafish as a Preclinical in vivo Screening Model for Nanomedicines” was selected by the Editor for the Editors’ Collection issue by Advanced Drug Delivery Reviews. It is one of the highlights of our study that the observations made in the zebrafish are highly predictive for experiments in rodents. To address the concern of the reviewer regarding the use of xenografted zebrafish, we added eight additional references and updated the “Discussion” section to highlight advantages and disadvantages of xenotransplanted zebrafish as follows:

Results and Discussion: “In recent years, several groups have used xenografted zebrafish for various investigations including the assessment of nanoparticles.(Sieber et al., 2019; Evensen et al., 2016; Wertman et al., 2016; Brown et al., 2017; He et al., 2012; Lin et al., 2017; Veinotte et al., 2014; Wagner et al., 2010) Despite anatomical differences with mammals, zebrafish xenotransplantation models are an emerging preclinical tool offering several practical advantages as compared to mouse xenografting models including prolific reproduction, facilitated xenotransplantation (no immune rejection due to limited adaptive immune response), and optical transparency enabling high throughput screening. For our study,…”

Reviewer #3:

This is an interesting study about the use of HBV targeting properties to achieve liver-specific delivery. The authors developed a potent liver-specific drug delivery carrier modified with an alternative liver-targeting moiety. They utilized the zebrafish and murine model to optimize and characterize the ligand-modified liposome. The liver-specific delivery carrier showed increased liver uptake and decreased off-target delivery to other tissues in murine models. In general, the article describes a well performed study. There are some major concerns:

1) Although the authors mentioned small molecule drugs, nucleic acids or proteins can be encapsulated and studied in appropriate disease models in the future. Lake of demonstration of further application may hamper the impact of this work. The authors should show the application of the carriers, which is a usual practice for high impact journals such as eLife. For example, does the liver-specific carrier increases plasmid DNA delivery and enhanced the transfection efficacy in livers sites?

The scope of this study is the development and in-depth optimization of NTCP-targeted nanoparticles using a unique approach of combining in vitro investigations and experiments in rodents with the emerging zebrafish model. in vivo liver transfection studies are beyond the scope of this manuscript. However, we performed an in vitro study to investigate the potential application of NTCP-targeted lipid nanoparticles as gene delivery systems. We successfully entrapped a DNA vector coding for GFP into lipid nanoparticles and modified their surface with Myr-preS2-31. These systems were tested in HepG2 SLC10A1 cells regarding their gene delivery efficacy. An additional figure was provided (Figure 1—figure supplement 9), additional methods and references were added, and the manuscript was updated as follows:

Results and Discussion: “In order to demonstrate the potential application of Myr-preS2-31 modified nanoparticles as drug delivery system, we successfully incorporated small molecular payloads as well as larger compounds into nanoparticles payloads (i.e. propidium iodide, doxorubicin, FITC-labeled peptide, DNA vector) to enhance their internalization into NTCP expressing cells (Figure 1—figure supplement 6, 7, 8 and 9) […] To investigate the potential application of NTCP-targeted lipid nanoparticles as gene delivery systems, we encapsulated a DNA vector coding GFP into lipid nanoparticles based on a clinically approved lipid composition and modified their surface with Myr-preS2-31. High content screening analysis demonstrated that modification of nanoparticles with Myr-preS2-31 significantly increases the transfection of NTCP expressing cells (Figure 1—figure supplement 9).”

Materials and methods: “DNA vector loading. Lipid nanoparticles entrapping DNA were prepared as previously described with modifications.(Kulkarni et al., 2019, 2018, 2017) Briefly, lipids (ionizable lipid, cholesterol, DSPC, DSPE-PEG2000, and DSPE-PEG2000-Maleimide at a molar ratio of 50:39:10:0.75:0.25 mol%) were dissolved in ethanol at a total lipid concentration of 15 mM. The DNA vector was dissolved in 25 mM sodium acetate (pH 4) at an N/P ratio of 6). After T-junction mixing at a flow rate ratio of 3:1 v/v, the pH was neutralized using a 5x excess of D-PBS, the appropriate amount of Myr-preS2-31 was added, and the resulting suspension was dialyzed against D-PBS to remove residual ethanol.”

“High-content screening. To quantify the transfection of HepG2 cells deficient or expressing NTCP using DNA loaded nanoparticles, high-content screening was performed as described previously.(Lin et al., 2013) Cells were seeded in 96-well cell culture dishes, were allowed to adhere for 24 h, and treated with lipid nanoparticles at a DNA concentration of 1.5 μg/mL. To assess the transfection efficacy using high-content screening, cells were fixed with 3% paraformaldehyde 24 h post treatment and cell nuclei were counterstained with Hoechst 33342. Plates were scanned and analyzed using a Cellomics ArrayScan VTI (Thermo Scientific).”

Figure 1—figure supplement 9: “Activity of DNA loaded lipid nanoparticles (LNP). LNP entrapping GFP coding DNA were modified with Myr-preS2-31 and compared to non-modified PEG DNA-LNP. (A) Representative fluorescence images of HepG2 SLC10A1 cells 24 h after PEG DNA-LNP and Myr-preS2-31 DNA-LNP treatment are shown. Blue signal: Hoechst stain of cell nuclei. Green signal: GFP expressing cells. CellOmics analysis was performed to quantify transfection efficiency. (B) Quantification of transfection efficiency. All values are shown as mean ± SD of biological replicates (n = 4 experiments). **p < 0.01.”

2) The fact that ASGPR-targeted delivery systems can improve gene/drug delivery has been already well studied. Although the authors defined their drug carriers as alternative approaches. The advantage and limitation of the alternative approaches should be highlighted and discussed.

We thank the reviewer for this comment. To clarify this point, we modified the conclusion section and included important drawbacks of ASGPR and LDLR-targeted delivery systems and illustrated a possible advantage of our system as follows:

Conclusion: “Despite the fact that current liver targeting strategies such as ASGPR- or LDLR-targeted delivery systems have already demonstrated improved drug and gene delivery in various preclinical models, these systems also suffer from certain drawbacks including complex synthesis of multivalent glycans or strong evidence that a majority of endocytosed gene carriers is recycled back to the cell exterior thereby reducing activity.(Witzigmann et al., 2016; Sahay et al., 2013) Due to the availability of efficient of peptide manufacturing protocols, the proposed NTCP targeted delivery platform is an alternative and promising approach which warrants further investigation. For future clinical applications, optimized Myr-preS2-31 conjugated nanoparticles entrapping small molecule drugs, nucleic acids or proteins need to be studied in appropriate animal models of disease.”

https://doi.org/10.7554/eLife.42276.042

Article and author information

Author details

  1. Dominik Witzigmann

    1. Division of Pharmaceutical Technology, Department of Pharmaceutical Sciences, University of Basel, Basel, Switzerland
    2. Department of Biochemistry and Molecular Biology, University of British Columbia, Vancouver, Canada
    Contribution
    Conceptualization, Resources, Formal analysis, Supervision, Funding acquisition, Validation, Visualization, Methodology, Writing—original draft, Project administration, Writing—review and editing
    For correspondence
    dominik.witzigmann@unibas.ch
    Competing interests
    No competing interests declared
    ORCID icon "This ORCID iD identifies the author of this article:" 0000-0002-8197-8558

  2. Philipp Uhl

    Department of Nuclear Medicine, University Hospital Heidelberg, Heidelberg, Germany
    Contribution
    Conceptualization, Formal analysis, Supervision, Funding acquisition, Validation, Investigation, Visualization, Methodology, Writing—original draft, Project administration, Writing—review and editing, Design and aquisition of rodent experiments
    Competing interests
    No competing interests declared

  3. Sandro Sieber

    Division of Pharmaceutical Technology, Department of Pharmaceutical Sciences, University of Basel, Basel, Switzerland
    Contribution
    Conceptualization, Formal analysis, Investigation, Methodology, Writing—review and editing, Design and aquisition of zebrafish experiments
    Competing interests
    No competing interests declared

  4. Christina Kaufman

    1. Department of Nuclear Medicine, University Hospital Heidelberg, Heidelberg, Germany
    2. Department of Infectious Diseases, Molecular Virology, University Hospital Heidelberg, INF, Heidelberg, Germany
    Contribution
    Conceptualization, Formal analysis, Investigation, Methodology, Writing—review and editing, Conception and design of HBV derived peptides and aquisition of rodent experiments
    Competing interests
    No competing interests declared

  5. Tomaz Einfalt

    Division of Pharmaceutical Technology, Department of Pharmaceutical Sciences, University of Basel, Basel, Switzerland
    Contribution
    Conceptualization, Formal analysis, Investigation, Methodology, Writing—original draft, Writing—review and editing, Physicochemical nanocarrier characterisation
    Competing interests
    No competing interests declared

  6. Katrin Schöneweis

    Department of Infectious Diseases, Molecular Virology, University Hospital Heidelberg, INF, Heidelberg, Germany
    Contribution
    Formal analysis, Investigation, Methodology, Writing—original draft, Acquisition of tissue staining, Analysis and interpretation of data
    Competing interests
    No competing interests declared

  7. Philip Grossen

    Division of Pharmaceutical Technology, Department of Pharmaceutical Sciences, University of Basel, Basel, Switzerland
    Contribution
    Formal analysis, Investigation, Methodology, Writing—original draft, Conception and design of nanocarrier
    Competing interests
    No competing interests declared
    ORCID icon "This ORCID iD identifies the author of this article:" 0000-0002-3416-5570

  8. Jonas Buck

    Division of Pharmaceutical Technology, Department of Pharmaceutical Sciences, University of Basel, Basel, Switzerland
    Contribution
    Investigation, Methodology, Writing—original draft, Acquisition of uptake mechanism studies
    Competing interests
    No competing interests declared

  9. Yi Ni

    Department of Infectious Diseases, Molecular Virology, University Hospital Heidelberg, INF, Heidelberg, Germany
    Contribution
    Conceptualization, Resources, Methodology, Conception and design of NTC expressing cell lines
    Competing interests
    No competing interests declared

  10. Susanne H Schenk

    Division of Pharmaceutical Technology, Department of Pharmaceutical Sciences, University of Basel, Basel, Switzerland
    Contribution
    Conceptualization, Resources, Investigation, Methodology, Writing—original draft, Writing—review and editing, Design of DNA vectors
    Competing interests
    No competing interests declared

  11. Janine Hussner

    Division of Biopharmacy, Department of Pharmaceutical Sciences, University of Basel, Basel, Switzerland
    Contribution
    Resources, Formal analysis, Methodology, Contributed unpublished essential data
    Competing interests
    No competing interests declared

  12. Henriette E Meyer zu Schwabedissen

    Division of Biopharmacy, Department of Pharmaceutical Sciences, University of Basel, Basel, Switzerland
    Contribution
    Conceptualization, Methodology, Writing—review and editing, Design of NTCP encoding DNA vectors
    Competing interests
    No competing interests declared
    ORCID icon "This ORCID iD identifies the author of this article:" 0000-0003-0458-4579

  13. Gabriela Québatte

    Division of Pharmaceutical Technology, Department of Pharmaceutical Sciences, University of Basel, Basel, Switzerland
    Contribution
    Conceptualization, Investigation, Contributed unpublished essential data
    Competing interests
    No competing interests declared

  14. Walter Mier

    Department of Nuclear Medicine, University Hospital Heidelberg, Heidelberg, Germany
    Contribution
    Conceptualization, Resources, Formal analysis, Funding acquisition, Writing—review and editing
    Competing interests
    No competing interests declared

  15. Stephan Urban

    Department of Infectious Diseases, Molecular Virology, University Hospital Heidelberg, INF, Heidelberg, Germany
    Contribution
    Conceptualization, Resources, Formal analysis, Funding acquisition, Writing—review and editing
    Competing interests
    No competing interests declared

  16. Jörg Huwyler

    Division of Pharmaceutical Technology, Department of Pharmaceutical Sciences, University of Basel, Basel, Switzerland
    Contribution
    Conceptualization, Resources, Formal analysis, Funding acquisition, Writing—original draft, Project administration, Writing—review and editing
    For correspondence
    joerg.huwyler@unibas.ch
    Competing interests
    No competing interests declared
    ORCID icon "This ORCID iD identifies the author of this article:" 0000-0003-1748-5676

Funding

Swiss National Science Foundation (174975)

  • Dominik Witzigmann

Swiss National Science Foundation (173057)

  • Jonas Buck
  • Jörg Huwyler

Deutsche Forschungsgemeinschaft (209091148)

  • Stephan Urban

German Center for Infection Research (5.704)

  • Stephan Urban

German Center for Infection Research (5.807)

  • Stephan Urban

Freiwillige Akademische Gesellschaft (FAG Basel)

  • Dominik Witzigmann
  • Sandro Sieber
  • Jörg Huwyler

Stiftung zur Förderung des pharmazeutischen Nachwuchses in Basel

  • Sandro Sieber

University of Basel (Novartis University Basel Excellence Scholarship for Life Sciences)

  • Dominik Witzigmann

Novartis (Novartis University Basel Excellence Scholarship for Life Sciences)

  • Dominik Witzigmann

The funders had no role in study design, data collection and interpretation, or the decision to submit the work for publication.

Acknowledgements

We thank M Affolter, HG Belting and N Schellinx for providing zebrafish eggs, K Leotta for support with mice experiments, S Meßnard for sectioning of paraffin-embedded tissue, P Scheiffele and L Burklé for support with cryo-sectioning, and H Heerklotz and D Eckhardt for DSC and PPC measurements.

Ethics

Animal experimentation: Animal experimentation: Zebrafish embryo (Danio rerio) studies were performed in strict accordance with Swiss animal welfare regulations. Mouse and rat experiments were carried out in accordance with German legislation on animal welfare. All of the animals were handled according to approved institutional animal care and use protocol of the University of Basel and University of Heidelberg.

Senior Editor

  1. Didier Y Stainier, Max Planck Institute for Heart and Lung Research, Germany

Reviewing Editor

  1. Bavesh D Kana, University of the Witwatersrand, South Africa

Reviewer

  1. Sjoerd Hak

Version history

  1. Received: September 24, 2018
  2. Accepted: July 17, 2019
  3. Accepted Manuscript published: July 23, 2019 (version 1)
  4. Version of Record published: August 5, 2019 (version 2)

Copyright

© 2019, Witzigmann et al.

This article is distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use and redistribution provided that the original author and source are credited.

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  1. Dominik Witzigmann
  2. Philipp Uhl
  3. Sandro Sieber
  4. Christina Kaufman
  5. Tomaz Einfalt
  6. Katrin Schöneweis
  7. Philip Grossen
  8. Jonas Buck
  9. Yi Ni
  10. Susanne H Schenk
  11. Janine Hussner
  12. Henriette E Meyer zu Schwabedissen
  13. Gabriela Québatte
  14. Walter Mier
  15. Stephan Urban
  16. Jörg Huwyler
(2019)
Optimization-by-design of hepatotropic lipid nanoparticles targeting the sodium-taurocholate cotransporting polypeptide
eLife 8:e42276.
https://doi.org/10.7554/eLife.42276

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