Review

Subcutaneous sustained-release drug delivery system for antibodies and proteins

  • Subcutaneous (SC) sustained release is an important drug delivery system (DDS) for antibody/protein drugs because it reduces dosing frequency. This review discusses formulations and biophysical parameters that affect the pharmacokinetics (PK) of DDSs. For example, SC injectable microspheres and polymeric hydrogels, as well as intradermal microneedles, suppress denaturation in loading and burst release of drugs [growth hormone, interferon-α2b, bevacizumab, and single-chain antibody fragment (scFv)]. These DDSs significantly prolong half-life (t1/2) in plasma with low maximum concentration (Cmax) and low relative bioavailability after SC dosing to animals and/or humans. Formulation parameters, such as (1) drug loading amount, (2) drug diffusion in DDS, (3) interactions of drugs with polymers, and (4) microneedle design, likely contribute to their PK profiles. This review also discusses the effects of many biophysical parameters on PK, including (5) in vivo behavior of polymers (swelling, aggregation, dissolution, and accumulation), (6) drug interactions with extracellular matrix and hypodermis diffusion, (7) drug unfolding, (8) hypodermic concentration of drugs, inherent proteins, and cells, (9) drug absorption through lymphatic or blood vessels, (10) degradation of drugs/polymers by proteases/phagocytic cells, (11) FcRn-mediated recycling, (12) FcγR-mediated endocytosis, and (13) target-mediated drug clearance. For safe dosing, (14) skin's thickness/viscoelastic properties and variations and (15) skin's recovery are also important factors. Consideration of these effects will increase the developmental speed and success of many SC sustained-release DDSs of antibody/protein drugs.

    Citation: Takayuki Yoshida, Hiroyuki Kojima. Subcutaneous sustained-release drug delivery system for antibodies and proteins[J]. AIMS Biophysics, 2025, 12(1): 69-100. doi: 10.3934/biophy.2025006

    Related Papers:

    [1] Ivana Sirangelo, Margherita Borriello, Gaetano Irace, Clara Iannuzzi . Intrinsic blue-green fluorescence in amyloyd fibrils. AIMS Biophysics, 2018, 5(2): 155-165. doi: 10.3934/biophy.2018.2.155
    [2] Alessandro Didonna, Federico Benetti . Post-translational modifications in neurodegeneration. AIMS Biophysics, 2016, 3(1): 27-49. doi: 10.3934/biophy.2016.1.27
    [3] Nick K. Olrichs, J. Bernd Helms . Novel insights into the function of the conserved domain of the CAP superfamily of proteins. AIMS Biophysics, 2016, 3(2): 232-246. doi: 10.3934/biophy.2016.2.232
    [4] Jany Dandurand, Angela Ostuni, Maria Francesca Armentano, Maria Antonietta Crudele, Vincenza Dolce, Federica Marra, Valérie Samouillan, Faustino Bisaccia . Calorimetry and FTIR reveal the ability of URG7 protein to modify the aggregation state of both cell lysate and amylogenic α-synuclein. AIMS Biophysics, 2020, 7(3): 189-203. doi: 10.3934/biophy.2020015
    [5] Nicola Gaetano Gatta, Gaetano Cammarota, Vittorio Gentile . Possible roles of transglutaminases in molecular mechanisms responsible for human neurodegenerative diseases. AIMS Biophysics, 2016, 3(4): 529-545. doi: 10.3934/biophy.2016.4.529
    [6] J. Dandurand, E. Dantras, C. Lacabanne, A. Pepe, B. Bochicchio, V. Samouillan . Thermal and dielectric fingerprints of self-assembling elastin peptides derived from exon30. AIMS Biophysics, 2021, 8(3): 236-247. doi: 10.3934/biophy.2021018
    [7] Daniela Meleleo, Cesare Sblano . Influence of cholesterol on human calcitonin channel formation. Possible role of sterol as molecular chaperone. AIMS Biophysics, 2019, 6(1): 23-38. doi: 10.3934/biophy.2019.1.23
    [8] Marek K. Korzeniowski, Barbara Baird, David Holowka . STIM1 activation is regulated by a 14 amino acid sequence adjacent to the CRAC activation domain. AIMS Biophysics, 2016, 3(1): 99-118. doi: 10.3934/biophy.2016.1.99
    [9] Nicole Shamitko-Klingensmith, Jonathan W. Boyd, Justin Legleiter . Microtubule modification influences cellular response to amyloid-β exposure. AIMS Biophysics, 2016, 3(2): 261-285. doi: 10.3934/biophy.2016.2.261
    [10] Yu-Ting Huang, Hui-Fen Liao, Shun-Li Wang, Shan-Yang Lin . Glycation and secondary conformational changes of human serum albumin: study of the FTIR spectroscopic curve-fitting technique. AIMS Biophysics, 2016, 3(2): 247-260. doi: 10.3934/biophy.2016.2.247
  • Subcutaneous (SC) sustained release is an important drug delivery system (DDS) for antibody/protein drugs because it reduces dosing frequency. This review discusses formulations and biophysical parameters that affect the pharmacokinetics (PK) of DDSs. For example, SC injectable microspheres and polymeric hydrogels, as well as intradermal microneedles, suppress denaturation in loading and burst release of drugs [growth hormone, interferon-α2b, bevacizumab, and single-chain antibody fragment (scFv)]. These DDSs significantly prolong half-life (t1/2) in plasma with low maximum concentration (Cmax) and low relative bioavailability after SC dosing to animals and/or humans. Formulation parameters, such as (1) drug loading amount, (2) drug diffusion in DDS, (3) interactions of drugs with polymers, and (4) microneedle design, likely contribute to their PK profiles. This review also discusses the effects of many biophysical parameters on PK, including (5) in vivo behavior of polymers (swelling, aggregation, dissolution, and accumulation), (6) drug interactions with extracellular matrix and hypodermis diffusion, (7) drug unfolding, (8) hypodermic concentration of drugs, inherent proteins, and cells, (9) drug absorption through lymphatic or blood vessels, (10) degradation of drugs/polymers by proteases/phagocytic cells, (11) FcRn-mediated recycling, (12) FcγR-mediated endocytosis, and (13) target-mediated drug clearance. For safe dosing, (14) skin's thickness/viscoelastic properties and variations and (15) skin's recovery are also important factors. Consideration of these effects will increase the developmental speed and success of many SC sustained-release DDSs of antibody/protein drugs.



    Alzheimer's disease (AD) is a fatal neurodegenerative disorder that is the most prevalent form of dementia. The neuropathological and neurochemical hallmarks of AD include: Synaptic loss and selective neuronal cell death; decreases in markers for certain neurotransmitters; and abnormalities in neurons and their processes as well as in the extracellular space. Two of the main features associated with AD are neurofibrillary tangles comprised of the protein tau and cerebrovascular, diffuse, and neuritic plaques composed predominantly of the amyloidogenic peptide amyloid-β (Aβ). These proteinaceous deposits of tau and Aβ consist of stable amyloid fibrils, which are β-sheet rich fibrous protein agammaegates. Similar deposition of amyloid is associated with numerous other diseases [1].

    In the early 90's, the amyloid cascade hypothesis was introduced, which postulated that Aβ agammaegation and deposition directly lead to neuronal death, resulting in AD [2]. Yet, the correlation between plaques and cognitive dysfunction in AD has been questionable for years [3][7], and with Aβ-directed therapeutic strategies failing in numerous clinical trials, the role of Aβ in AD progression is being re-evaluated [8][11]. This has led to an enhanced research focus on diffuse, soluble agammaegates of Aβ. Various small, globular agammaegates of Aβ, referred to broadly as Aβ oligomers (AβO), were detected in AD patients a few decades ago [12][14], and these AβO were originally classified as being intermediates toward the formation of amyloid fibrils. Over the years, increasing evidence points toward AβOs playing a central role in AD, as AβOs correlate more strongly with AD progression in patients and animal models [15][19]. For example, AβO formation and buildup occurs early compared with plaque buildup (much earlier than plaque deposition) in the AD brain [20][22]and CSF [23], which has led to extensive efforts to develop assays to detect AβOs for potential application as biomarkers [24][31].

    An extensive body of evidence has linked high levels of AβOs in the brain to a variety of pathogenic consequences associated with AD (summarized in Table 1). As such, there has been significant effort made to characterize AβO formation, structure, and biochemical/biophysical characteristics (such as interactions with other proteins and lipids) in the hope that underlying modes of AβO-related toxicity could be revealed [32][37]. As AβOs are metastable, highly heterogeneous in nature, and can form via a variety of different pathways, this remains a challenging task, yet progress has been made. Here, we review AβOs with a focus on biophysical characterization of their formation and structure.

    Table 1.  Toxic mechanisms associated with AβOs.
    Toxic effects of AβOs Model system(s) References
    Reduction in neural plasticity mice, rat [37][40]
    Stimulation of tau phosphorylation cortical neurons (rat), hippocampal neurons, neuroblastoma, primary neurons, Tg-Mice [41][45]
    Choline acetyltransferase Inhibition cholinergic cell lines [46],[47]
    Oxidative stress cortical neurons, hippocampal neurons, in vitro, neuroblastoma [48][51]
    Endoplasmic reticulum stress cortical astrocytes, cortical neurons (rat), fibroblasts, Tg-mice [43],[52],[53]
    Receptor disturbance cortical neurons, hippocampal neurons [54][57]
    Insulin resistance cortical neurons, hippocampal neurons, rat [40],[42],[57],[58]
    Synapse deterioration hippocampal neurons, pyramidal neurons (rat), Tg-mice [21],[35],[54],[59]
    Axonal transport cortical neurons, hippocampal, in vitro, Tg-mice [60][62]
    Astrocytes/microglia effects cortical astrocytes, Tg-mice [44],[52],[63],[64]
    Cell cycle disruption cortical neurons, Tg-mice [65],[66]
    Selective neuron death Mice [38],[67]
    Inhibition of long-term potentiation Mice [37],[40]
    Calcium dysregulation cortical neurons (rat), hippocampal neurons, primary neurons [43],[45],[48],[52]
    Modulation of metal toxicity neuroblastoma [49]
    Cytoskeleton disruption primary neurons [50]
    Modulation of Receptor/Channel Activity hippocampal neurons [48]

     | Show Table
    DownLoad: CSV

    Aβ is an approximately 4 kDA peptide (typically 40–42 amino acids long) that is derived from the transmembrane portion of the amyloid precursor protein (APP; Figure 1). The production of Aβ is achieved by the sequential cleavage of APP by two membrane-bound endoprotease activities, β- and γ-secretase. The two predominant Aβ peptides produced are 40 and 42 amino acids in length, and these peptides are referred to as Aβ40 and Aβ42 respectively. Aβ is amphipathic in nature (having a predominately hydrophilic N-terminus and a predominately hydrophobic C-terminus), which is thought to drive its agammaegation. As the C-terminal end of Aβ coincides with the transmembrane portion of APP, Aβ42 has a larger hydrophobic domain, making it more fibrillogenic compared to Aβ40 and deposits to a much greater extent in the brain [68][70]. Only about 10% of APP is processed via this Aβ producing pathway. Most APP is cleaved by the α-secretase, generating a series of much more benign peptide fragments.

    The hydrophilic N-terminal region of Aβ can adopt both an α-helical or β-sheet structure dependent on solution conditions, for example pH [71],[72]. The hydrophobic C-terminal end of Aβ has a propensity to adopt β-sheet structure upon agammaegation independent of solvent conditions [71],[72]. Beyond its amphipathic nature, several other domains have been identified in Aβ. The different polyomorphic fibril structures of Aβ are comprised of bundled β-sheets with backbones orthogonal to the fiber axis creating a cross-β structure [73], and two β-strand forming domains (residues 11–21 and 29–39 respectively) that are separated by a turn/bend region (around residues 23–26) identified through various experimental and computational studies [74][77]. The central region of Aβ (residues 16–21), contained within one of the β-strands, has enhanced amyloidogenic properties and represents a hydrophobic core [78].

    Figure 1.  APP processing and subsequent Aβ amino acid sequence with specific domains of interest specified. Proteolytic cleavage of APP is initiated at residue 671 by β-secretase followed by either non-amyloidogenic processing, cleavage at residue 687 by α-secretase, or amyloidogenic processing, cleavage at residue 711, 713, 714, or 726 by γ- secretase. The amino acid sequence below highlights the region of APP from which Aβ is produced with the numbering referring the residues in Aβ. The orange highlighted region represents the intact Aβ42 sequence. Hydropathy indexes of individual residues are color coded according to hydrophobic (blue), slightly hydrophobic (light green), and hydrophilic (red). Regions of interest and cites of secretase activity within the APP and Aβ are indicated.

    The agammaegation of Aβ (and other amyloid-forming proteins) is typically characterized in terms of fibril formation (Figure 2). Aβ fibril formation occurs via a complex agammaegation pathway. Fundamentally, AβOs can be subdivided into species that are intermediates in fibrils formation (referred to as being on pathway) or species that do not directly lead to fibrils (referred to as being off pathway). This is a contributing factor to the immense heterogeneity observed in AβO populations as will be discussed in more detail later. In general, amyloid formation proceeds via a nucleation dependent polymerization mechanism [79][81]. With this mechanism, agammaegation initially occurs via a slow nucleation phase (often called the lag phase) that involves the formation of a thermodynamically unfavorable critical nucleus that is associated with a transition from a native to non-native protein conformation. For Aβ, the critical nucleus is likely a multimeric species [82][84]. Once the critical nucleus has formed, an elongation or growth phase (characterized by a relatively rapid extension of fibril agammaegates) occurs. While numerical models can extract important parameters (lag phase times, elongation rates, critical nucleus size) from experimental data [85], the actual agammaegation pathway toward fibrils can be complicated. For example, other on pathway intermediates, like protofibrils, are also observed in Aβ agammaegation. Protofibrils are amyloid-like, elongated agammaegates with filament-like morphologies and are late-stage intermediate precursors on the agammaegation pathway to fibrils. A key aspect that facilitates on and off pathway agammaegation routes and complicates investigations of AβOs is that they possess structural plasticity and are metastable and transient in nature.

    Figure 2.  Production and aggregation Aβ. Aβ is a cleavage product of APP, a transmembrane protein. Monomeric Aβ transitions between ordered and disordered states. Once dimerization occurs, subsequent aggregation occurs either on pathway or off pathway with respect to fibril formation. The aggregates associated with these different pathways increase in molecular weight from the left to the right of the schematic. Fibrillization can proceed via several potential pathways that can populate various intermediate aggregate states, including oligomers and protofibrils. Off-pathway oligomers of various size may also form. Annular aggregates of Aβ can also form and are thought to potentially be associated with forming pore-like structures.

    Further complicating the issue is the observation that Aβ can agammaegate into a variety of morphologically distinct fibril structures, referred to as polymorphs [86][90]. This phenomenon is predicated on subtle changes of environmental conditions associated with agammaegation, and as a result, preparatory protocols employed in experiments determines the resulting Aβ fibril morphology [87]. While polymorphic agammaegates are readily observed with in vitro studies using synthetic Aβ, polymorphic structures have been observed in amyloids derived from tissue, and it is thought that variations in Aβ agammaegate morphologies may play an important role in AD [91],[92]. For example, polymorphic agammaegates and fibrils may result in distinct biological activities and levels of toxicity that could underlie variations in AD [76], and distinct fibril structures can be directly associated with individual AD patients and clinical phenotype [93],[94].

    A complicating factor in evaluating and comparing studies aimed at elucidating AβO formation, structure, and physiological impact is divergent experimental conditions, such as Aβ preparation protocols, heavily influences experimental outcomes. In terms of oligomers, the emergence of distinct fibril structure strongly suggests that there would also be distinct oligomeric precursors associated with their formation. Indeed, distinct AβO species can be observed within in vitro agammaegation assays under conditions that result in fibril polymorphs [95] (Figure 3). For studies conducted with synthetic peptide, there are a variety of protocols used to solubilize Aβ (Table 2). Typically, these protocols consist of a disagammaegation step and a reconstitution step. The disagammaegation steps usually involves the use of hydrogen bond disrupting solvents, i.e., hexafluoroisopropanol (HFIP) or trifluoroacetic acid (TFA), that break down pre-existing agammaegates within lyophilized stocks of Aβ. These solvents are often removed under vacuum, leaving a peptide film. The reconstitution step involves dissolving these peptide films into a solvent that facilitates dilution into an appropriate buffer. Dimethyl sulfoxide (DMSO) is often used, creating a concentrated stock that is diluted into the desired buffer. Disagammaegation and reconstitution can also be facilitated by changes in pH. Sometimes reconstitution is performed directly into the final buffer. Importantly, variations in preparatory protocols indeed result in different populations of oligomers (Table 2 and Figure 3), and these variations can complicate direct comparisons between different reports within the literature. Further complicating the issue, there are often distinctions observed between studies performed with synthetic Aβ and naturally derived Aβ [96]. In many studies aimed at elucidating activity of AβOs, specific preparations are used to obtain a particular population of oligomer species. These are then directly applied to different model systems, ranging from cell culture to animal models. However, there is often a lack of effort to verify that once added to the model system (which can often be a pronounced change in chemical environment) that these AβO species do not dissociate or agammaegate into a different AβO or Aβ agammaegate. To truly relate specific AβOs to a neurotoxic activity, effort should be invoked to attempt additional controls of this type.

    Table 2.  Representative disaggregation, reconstitution, and miscellaneous protocols for the preparation of Aβ and observed AβOs.
    Classification Disaggregation Reconstitution Miscellaneous Result References
    ADDLs None F12 Media 4 °C Centrifuged 14,000 ×g for 10 mins 5–6 nm by AFM (height) [38]
    ADDLs HFIP DMSO at 5 mM Aβ Sonicate 5 mins, dilute with DMEM/F12 Media A11+ [97]
    Globulomers HFIP DMSO at 5 mM Aβ Sonicate 10 mins, dilute PBS + 0.05% SDS 16–56 kDa by SDS-PAGE [98]
    Globulomers HFIP DMSO at 5 mM Aβ Dilute PBS + 0.05% SDS, Dialyze 38–48 kDa by SDS-PAGE [99]
    Aβ*56 HFIP DMSO at 5 mM Aβ Sonicate 20 min, PBS + 0.2% SDS incubate 6 h, dilute and incubated 18 h; centrifuge 3000 ×g, dialysis 56 kDa by Native-PAGE [100]
    AβOs HFIP DMSO F12 Media incubated at 4 °C for 24 h 1–4 nm by AFM [101],[102]
    AβOs HFIP/NH4OH 10 mM Tris-HCl Addition of Zn2+ 10–12 nm by AFM [97]
    AβOs TFA/HFIP (2Xs) 2 mM NaOH PBS Centrifuge 386,000 ×g 2.5 nm by AFM [87],[95]
    AβOs TFA salt/2 mM NaOH, pH ∼10.5, 1 min sonication HH PBS - 3–12 nm by AFM [103]
    AβOs 10% NH4OH (w/v) sonicated 5 mins, lyophilized 60 mM NaOH - 1–10 nm by DLS [104]
    AβOs LMW - DMSO Sonicate 1 min, centrifuge 16,000 ×g, SEC, PBS, PICUP crosslinking 4–26 kDa by SDS-PAGE [105]

     | Show Table
    DownLoad: CSV
    Figure 3.  Heterogeneity of AβOs. A series of atomic force microscopy images and size analysis, i.e. height histograms, of AβOs formed from synthetic Aβ that had been prepared by some of the protocols described in Table 2. The AβOs were prepared in the following way: (A) protocol provided in the AggreSure β-amyloid kits available from AnaSpec which consists of a reconstitution step directly into Tris buffer with bath sonication; (B) 10% NH4OH disaggregation buffer, followed by additional treatment with HFIP, and reconstitution in 2 mM NaOH (pH > 11) with subsequent dilution into Tris buffer; (C) 10% NH4OH disaggregation buffer, and reconstitution in 60 mM NaOH (pH > 11) with subsequent dilution into HEPES buffer; (D) HFIP disaggregation, reconstitution in DMSO, followed by dilution into PBS; (E) TFA disaggregation with sonication, an additional HFIP disaggregation step, reconstitution with NaOH, and dilution into PBS; (F) No disaggregation step and direct reconstitution in to phosphate buffer.

    Enormous efforts have been extended in identifying the most toxic/disease-relevant AβO species and the relevant underlying structure [9],[106],[107]. This is a daunting endeavor due to the transient nature and extensive heterogeneity associated with AβOs [108][110]. It is possible that different AβO species may activate different deleterious changes associated with AD [9],[106],[107]; however, there may also be relatively benign AβO species or even experimental artifacts [96],[108],[111]. Unraveling the physiological activity of AβOs may require separate analysis of these different species, which may be altered by preparatory protocols. The ability of smaller AβO (like dimers and trimers) to further agammaegate into large, more stable synaptotoxic assemblies [107] must be accounted for in assessing the toxic effects of specific AβO species. That is, upon the addition of preparations of AβO to cell culture or other models, AβOs may further assemble into other higher order species that may influence the associated toxic effects. Despite the inherent complexity of this endeavor, progress has been made. Aβ trimers have been linked to playing a role in inducing pathological conformational changes in tau [112]. However, crosslinked Aβ dimers were shown not to be toxic themselves, but rather contributed to toxicity by further assembling into larger assemblies [113]. A 56 kDa SDS-stable Aβ0 (referred to as Aβ*56) has been identified as a prominent specie in the AD brain [16], CSF [22], and in transgenic mouse models of AD [32],[114]. In terms of an actual biological activity, Aβ*56 interacts with N-methyl-D-aspartate receptors (NMDARs), increasing NMDAR-dependent Ca2+ influx and activation of Ca2+/calmodulin-dependent kinase IIα (CAMKIIα) [115]. Activation of CAMKIIα correlates with enhanced site-specific phosphorylation and mis-sorting of tau [115]. Smaller AβOs, namely dimers and trimers, do not appear to elicit these specific effects.

    There appears to be some common themes emerging with respect to toxicity. Toxic AβOs appear to react with oligomer specific antibodies like A11 (generic for amyloid oligomers in general, [116]) and NU4 (specific for AβOs) [117]; whereas, nontoxic AβOs demonstrate reactivity with anti-fibril antibodies like OC [116]. Importantly, toxic AβOs appear to be unrelated to plaques [116],[118]. AβOs related to amyloid plaques temporally, spatially, and structurally are nontoxic [118]. A number of toxic AβO species are larger than 50 kDa [21],[54],[118], like the previously mentioned Aβ*56 [32]. Smaller AβOs appear to be less toxic or even benign [21],[54],[118],[119], except for their ability to further agammaegated into larger assemblies. This has led to distinguishing between high molecular weight (HMW) and low molecular weight (LMW) oligomers [120]. Agammaegation mechanisms differentiating between the eventual formation of HMW and LMW AβOs already appear to deviate at the dimer stage [121]. Furthermore, LMW and HMW Aβ oligomers differentially impact synapses and memory [122],[123]; although, LMW AβOs are not always associated with memory dysfunction [116],[117]. HMW AβOs are the predominant Aβ species in the native soluble protein fraction of AD brains [124]. These HMW species in the AD brain sometimes appear to be constructed from smaller ∼7 kDa Aβ species [125]. Neurohistopathological and biochemical analyses of AβOs in the temporal cortex of AD brains implicated an Aβ dodecamer (∼55 kDa) [126]. HMW AβOs bind cultured synapses [21],[54],[118], induce reactive oxygen species (ROS) production [123], and disrupt memory function [116],[117]. With respect to the previously defined agammaegation pathways, LMW AβOs are typically on pathway to fibril formation; HMW AβOs are off-pathway [127],[128]. This is consistent with HMW AβOs being potent, as off pathway AβOs appear more toxic [129]. Collectively, these observations point to the complex interplay between different AβO species and their specific activity with respect to neurotoxicity.

    Table 3.  Methods used for analyzing AβOs.
    Technique Features of AβOs Obtained
    Atomic Force Microscopy (AFM) Morphology, population distributions
    Electron Microscopy (EM) Morphology, population distributions
    Ion-Mobility Mass Spectroscopy (IM-MS) Secondary structure, multimeric configurations
    Nuclear Magnetic Resonance 2D (NMR) Secondary structure, multimeric configurations, atomic resolution structure
    Electron Paramagnetic Resonance (EPR) Secondary structure, multimeric configurations, atomic resolution structure
    Powder X-ray Diffraction (PXRD) Atomic resolution structure
    Small Angle X-ray Scattering (SAXS) Atomic resolution structure
    Single Crystal X-ray Diffraction (SCXD) Atomic resolution structure
    SDS-Page Size distribution of multimers

     | Show Table
    DownLoad: CSV

    To facilitate structure/activity analysis, significant efforts have been made to obtain structural details of AβOs using a variety of methods (Table 3). This is required to fully elucidate the modes of interaction of AβOs with other biomolecules and related toxic mechanisms [32],[33],[35][37],[130]. Structural characterization of specific AβOs is challenging due to their transient nature and heterogeneity. AβOs can exhibit conformational plasticity that can be heavily influenced by environmental factors, further complicating such analysis. Despite these inherent challenges, efforts have been made to separate, isolate, and characterize distinct AβO species obtained from synthetic Aβ or from AD brain tissue and cell cultures [18],[32],[35][37],[114],[129],[131][136]. With regard to HMW and LMW AβOs, they are separable in vitro by size exclusion chromatography [137] or ultrafiltration with a 50 kDa molecular weight cutoff [21],[54],[118]. Quick characterization of AβOs can be accomplished by chromatographic techniques, SDS PAGE, and by the use of a variety of oligomer specific antibodies (Table 4).

    Table 4.  Anti-AβO specific antibodies.
    Antibody Epitope References
    A11 Soluble amyloid oligomers [17],[138]
    NAB61 Dimeric, oligomeric, higher order aggregates [139]
    NU-1 ADDLs specific [140]
    NU-2 ADDLs weak binding; no Aβ monomer staining [140]
    NU-4 ADDL trimer, tetramer, and 12–24 mer specific [140]

     | Show Table
    DownLoad: CSV

    One strategy that has been used to overcome obstacles associated with characterizing AβOs has been to stabilize oligomers via cross-linking. Such methods can lead to not only structural but also functional characterization of AβOs. Photo-induced crosslinking (PICUP) was initially used to stabilize and characterize LMW AβOs of Aβ40 and Aβ42 [33],[141][143].While Aβ40 primarily formed an equilibrium of dimers, trimers, and tetramers, Aβ42 agammaegated into pentamers/hexamers that further assembled into protofibrils [143]. Using mutated Aβ42 (F10, Y42), AβOs ranging from dimer to dodecamers were stabilized using PICUP [141], opening up the ability to perform structure/activity analysis on AβOs up to 50 kDa in size. AβOs can also be stabilized using dityrosine crosslinking, which occurs under elevated copper concentrations and oxidative stress [144]. Both of these conditions have been linked to AD, suggesting that the crosslinking associated with this method may be more physiologically relevant [145],[146]. In fact, dityrosine crosslinked proteins are observed in amyloid plaques and CSF from AD patients [145]. Dityrosine linkages are associated with copper-mediated stabilization of AβOs [147]. Copper stabilization is effective enough to allow for 3D structural characterization of AβOs by small-angle x-ray scattering [148], and the copper to Aβ ratio could push agammaegation toward ellipsoidal oligomers of 38 peptides (excess copper) or fibrils (excess Aβ) [119].

    Another method to overcome the metastability of Aβ species and control the agammaegation process is to complex/fuse Aβ sequences within other protein. Aβ sequences are often based on previously identified regions of the peptide that have been identified as playing a role in Aβ agammaegation (Figure 1). Such a strategy has been successful in studying monomeric structure of Aβ sequences [149]. With careful design, this method has been applied to stabilizing oligomers derived from Aβ fragments for structural characterization. Fusion of Aβ18–41 with the CDR3 loop region of a shark Ig new antigen receptor single variable domain antibody resulted in the formation and stabilization of tightly associated Aβ dimers, which could pair to form tetramers [150]. This dimer had a compact structure rather than a β-turn/β-sheet structure. Several engineered peptide macrocycles that incorporate Aβ sequences (Aβ15–23 and Aβ17–36) have been designed to contain agammaegation to the oligomeric state, and these systems have been structurally characterized by X-ray crystallography and NMR spectroscopy [151][153]. Collectively, this macrocycle strategy has revealed numerous dimers, trimers, tetramers, and higher order oligomer species that display a variety of β-sheet based structural heterogeneity.

    Due to the complex nature of Aβ agammaegation, techniques that allow for distinguishing and characterizing distinct morphological features of AβOs within heterogeneous agammaegation reactions are of enormous benefit. Both atomic force microscopy (AFM) and electron microscopy (EM) provide this capability. In particular, AFM has emerged as a particularly useful technique in studying AβO formation and morphology [95],[101],[134],[135],[154][160]. As AFM can be operated in solution, it has the ability to observe and track the behavior of individual AβOs on surfaces under physiological buffer conditions [158],[160]. The surfaces used in AFM experiments have become progressively more biologically relevant and include lipid membranes [135],[161][164]. With regard to Aβ agammaegation on lipid membranes, in solution AFM studies have demonstrated the formation of distinct oligomeric agammaegates associated with point mutation in Aβ [165], the formation of pore-like AβO morphologies [154][156], that preparation history influences AβO formation on bilayers [95], and that mechanical changes occur in bilayers associated with the presence of AβOs [166]. AFM based force spectroscopy has even been used to understand the energetics of AβO formation and stability [167],[168].

    With the recent development of high-speed AFM in solution, insights into the dynamics and fate of individual AβOs has been achieved [128],[169]. Using high-speed AFM to track the dynamics of PICUP-stabilized LMW AβOs demonstrated that these AβOs were highly dynamic in structure, fluctuating between single and multi-globular assemblies [169]. Direct visualization of Aβ agammaegation with high-speed AFM imaging demonstrates that LMW AβOs much more quickly transition to form fibrils with distinct morphologies compared with HMW AβOs [128]. Despite being classified as being off-pathway, HMW AβOs can still contribute to fibril formation by serving as a reservoir of Aβ. That is, HMW AβOs may dissociate into smaller LMW AβO that seed fibrillization [128]. This again points to the necessity to track the fate of AβO species when evaluating their physiological activities. For example, the LMW AβOs that are dissociation products of HMW AβOs may actually be more toxic [170].

    Another technique that is capable of characterizing heterogeneous populations of AβOs is ion mobility mass spectrometry (IM-MS). These IM-MS studies ascertained qualitative differences in AβO structure associated with Aβ40 and Aβ42 [131],[132]. Aβ40 tetramers displayed an enclosed ring-shaped configuration that would inhibit additional contacts required to assemble into larger AβO species [131],[132]. Aβ42 tetramers preferentially had a bent structure that would provide oligomer ends capable of additional contacts and enabling further agammaegation. Indeed, Aβ42 was capable of forming larger donut-shaped dodecamers.

    Another strategy to perform structural analysis of AβOs is utilizing specific conditions to stabilize them via a kinetic trap. Such an approach has been successfully used to enable NMR spectroscopy of AβOs [171],[172]. By incubation of Aβ at 4 °C and freeze-trapping with liquid nitrogen, heterogeneous, spherical AβOs were analyzed with 2D NMR and shown to possess in-register parallel β-strand structure similar to fibrils [172]. Based on NMR analysis, Aβ42 pentamers stabilized at a low 4 °C and 10 mM salt concentration were disordered [171]. These Aβ42 pentamers displayed enhanced toxicity compared with protofibrils or fibrils [171]. An atomic model of Aβ42 oligomers consisting of approximately 15–24 peptides has been proposed from a combination of biophysical techniques [173]. These oligomers were prepared by disagammaegation in HFIP followed by resuspension in dilute ammonium hydroxide, preventing fibril formation. These were not end-stage AβOs, as subsequent dilution in PBS resulted in fibril formation. Powder X-ray diffraction patterns of the AβOs were consistent with helical β-sheet pairs wrapped together into a super-helix. This wrapping results in a hole along the super-helix axis, which is consistent with proposed toxic mechanisms in which Aβ forms pathogenic pores. Another proposed structure, based on site-directed spin labeling and electron paramagnetic resonance, shares similarities with this structure [174]. This study used Aβ42 fused to GroES-ubiquitin that formed stable oligomers that were A11 positive. Based on the EPR data, an AβO model was proposed that consisted of a β-sheet with three antiparallel strands with these strands being arranged head to tail. These sheets are further packed face to back as a group of four.

    Even just tracking AβO formation has been challenging. A number of straight forward spectroscopic assays are well-established to track formation and kinetic parameters of fibrils (e.g., ThT), but methods to easily track AβO formation have been lacking. Recently, the use of 4,4-difluoro-4-bora-3a,4a-diaza-s-indacene (BODIPY) dyes have been utilized to fluorescently detect the AβOs in vitro [175],[176]. These BODIPY fluorescent probes have high quantum yields with the capability of selectively binding to AβOs [177]. Importantly, increases and decreases in the “BD-Oligo” dye fluorescence also correlated with increasing and decreasing intensities of A11 staining, directly relating this signal to an established methods to detect AβOs [175]. In addition, the BD-Oligo dye can be used in parallel with ThT assays that detect fibril formation, allowing for the direct investigation of the correlation between oligomer and fibril formation [175]. A BODIPY-based probe (BAP-1) has also facilitated the direct visualization of Aβ plaques in transgenic mice [177], and rational modifications of BAP-1 also allowed for near-infrared selective detection of tau neurofibrillary tangles [178]. The ability to rationally modify BODIPY dyes for fluorescent detection of specific agammaegate species, the tunability of their spectroscopic properties, and their insensitivity to solvent and pH changes have made BODIPY dyes a recently promising avenue for high throughput studies of AβO formation and stability.

    While the agammaegation of Aβ has been extensively studied, there is still much to understand at the molecular level about AβO formation, structure, and activity. Due to the transient nature of AβOs, their morphological heterogeneity, and the continuing debate concerning specific toxic agammaegate species associated with AD, structural details and physiological activities of the variety of AβOs still need to be fully elucidated. The exact mechanisms associated of how AβOs lead to cellular dysfunction and death have not fully been explained. Understanding these phenomenon may prove crucial in the effectiveness of therapeutic strategies based on manipulating Aβ production, clearance, and agammaegation. Here, we highlighted some specific features of AβOs and techniques that have provided insight into their structure and formation. While this review is far from exhaustive, we hope that collectively they provide a compelling argument toward the importance of understanding the nature of AβOs, highlight some of the intrinsic obstacles associated with studying AβOs, and provide some insight into methods that will play a role in pushing our knowledge of AβOs further.


    Acknowledgments



    This work was supported by Astellas Pharma Inc.

    Conflict of interest



    The authors are employees of Astellas Pharma Inc. The authors declare no conflict of interest.

    Author contributions



    The two authors substantially contributed to the conception and design of this manuscript, and the analysis and interpretation of data. The authors drafted this work, reviewed it critically for important intellectual content, and finally approved the version to be published. The authors agree to be accountable for all aspects of this work in ensuring that questions related to the accuracy or integrity of any part of this work are appropriately investigated and resolved.

    [1] Martin KP, Grimaldi C, Grempler R, et al. (2023) Trends in industrialization of biotherapeutics: a survey of product characteristics of 89 antibody-based biotherapeutics. MAbs 15: 2191301. https://doi.org/10.1080/19420862.2023.2191301
    [2] Shepard HM, Phillips GL, Thanos CD, et al. (2017) Developments in therapy with monoclonal antibodies and related proteins. Clin Med 17: 220-232. https://doi.org/10.7861/clinmedicine.17-3-220
    [3] Lu RM, Hwang YC, Liu IJ, et al. (2020) Development of therapeutic antibodies for the treatment of diseases. J Biomed Sci 27: 1. https://doi.org/10.1186/s12929-019-0592-z
    [4] Zhou Y, Zhang Y, Chen Z, et al. (2024) Dynamic clinical success rates for drugs in the 21st century. medRxiv . https://doi.org/10.1101/2024.02.26.24303388
    [5] Ovacik M, Lin K (2018) Tutorial on monoclonal antibody pharmacokinetics and its considerations in early development. Clin Transl Sci 11: 540-552. https://doi.org/10.1111/cts.12567
    [6] Morales JO, Fathe KR, Brunaugh A, et al. (2017) Challenges and future prospects for the delivery of biologics: oral mucosal, pulmonary, and transdermal routes. AAPS J 19: 652-668. https://doi.org/10.1208/s12248-017-0054-z
    [7] Gill HS, Denson DD, Burris BA, et al. (2008) Effect of microneedle design on pain in human volunteers. Clin J Pain 24: 585-594. https://doi.org/10.1097/AJP.0b013e31816778f9
    [8] Parra A, Hernández C, Prieto-Pinto L (2023) Evaluation of the economic benefits, administration times, and patient preferences associated with the use of biotechnological drugs administered subcutaneously and intravenously in patients with cancer: a systematic review. Expert Rev Pharmacoecon Outcomes Res 23: 1017-1026. https://doi.org/10.1080/14737167.2023.2249232
    [9] Tomasini L, Ferrere M, Nicolas J (2024) Subcutaneous drug delivery from nanoscale systems. Nat Rev Bioeng 2: 501-520. https://doi.org/10.1038/s44222-024-00161-w
    [10] Epstein RS (2021) Payer perspectives on intravenous versus subcutaneous administration of drugs. Clinicoecon Outcomes Res 13: 801-807. https://doi.org/10.2147/CEOR.S317687
    [11] Anderson KC, Landgren O, Arend RC, et al. (2019) Humanistic and economic impact of subcutaneous versus intravenous administration of oncology biologics. Future Oncol 15: 3267-3281. https://doi.org/10.2217/fon-2019-0368
    [12] Cappuzzo1 F, Zvirbule Z, Korbenfeld EP, et al. (2024) 244mo primary results from imscin002: a study to evaluate patient (pt)- and healthcare professional (hcp)-reported preferences for atezolizumab (atezo) subcutaneous (sc) vs intravenous (iv) for the treatment of NSCLC. EMBO Open 9: 102706. https://doi.org/10.1016/j.esmoop.2024.102706
    [13] Knowles SP, Printz MA, Kang DW, et al. (2021) Safety of recombinant human hyaluronidase ph20 for subcutaneous drug delivery. Expert Opin Drug Deliv 18: 1673-1685. https://doi.org/10.1080/17425247.2021.1981286
    [14] Bittner B, Schmidt J (2024) Advancing subcutaneous dosing regimens for biotherapeutics: clinical strategies for expedited market access. BioDrugs 38: 23-46. https://doi.org/10.1007/s40259-023-00626-1
    [15] Leconet W, Liu H, Guo M, et al. (2018) Anti-PSMA/CD3 bispecific antibody delivery and antitumor activity using a polymeric depot formulation. Mol Cancer Ther 17: 1927-1940. https://doi.org/10.1158/1535-7163.MCT-17-1138
    [16] Kasse CM, Yu AC, Powell AE, et al. (2023) Subcutaneous delivery of an antibody against SARS-CoV-2 from a supramolecular hydrogel depot. Biomater Sci 11: 2065-2079. https://doi.org/10.1039/d2bm00819j
    [17] Van Beers MMC, Slooten C, Meulenaar J, et al. (2017) Micro-flow imaging as a quantitative tool to assess size and agglomeration of PLGA microparticles. Eur J Pharm Biopharm 117: 91-104. https://doi.org/10.1016/j.ejpb.2017.04.002
    [18] Abulateefeh SR (2023) Long-acting injectable PLGA/PLA depots for leuprolide acetate: successful translation from bench to clinic. Drug Deliv Transl Re 13: 520-530. https://doi.org/10.1007/s13346-022-01228-0
    [19] Sali SR, Gondkar SB, Saudagar RB (2018) A review on: atrigel—the magical tool. Int J Curr Pharm Res 8: 48-54. https://doi.org/10.22159/ijcpr.2018v10i2.25890
    [20] Tornøe CW, Agersø H, Nielsen HA, et al. (2004) Population pharmacokinetic modeling of a subcutaneous depot for GnRH antagonist degarelix. Pharm Res 21: 574-584. https://doi.org/10.1023/b:pham.0000022403.60314.51
    [21] Fatima H, Shukrullah S, Hussain H, et al. (2023) Utility of various drug delivery systems and their advantages and disadvantages. Nanotechnology for Drug Delivery and Pharmaceuticals. New York: Academic Press 235-258. https://doi.org/10.1016/B978-0-323-95325-2.00015-8
    [22] Hoffman AR, Biller BMK, Cook D, et al. (2005) Efficacy of a long-acting growth hormone (gh) preparation in patients with adult gh deficiency. J Clin Endocrinol Metab 90: 6431-6440. https://doi.org/10.1210/jc.2005-0928
    [23] McKay WF, Peckham SM, Badura JM (2007) A comprehensive clinical review of recombinant human bone morphogenetic protein-2 (INFUSE bone graft). Int Orthop 31: 729-734. https://doi.org/10.1007/s00264-007-0418-6
    [24] Chen Z, Kankala RK, Yang Z, et al. (2022) Antibody-based drug delivery systems for cancer therapy: mechanisms, challenges, and prospects. Theranostics 12: 3719-3746. https://doi.org/10.7150/thno.72594
    [25] Ojaimi YA, Blin T, Lamamy J, et al. (2022) Therapeutic antibodies—natural and pathological barriers and strategies to overcome them. Pharmacol Ther 233: 108022. https://doi.org/10.1016/j.pharmthera.2021.108022
    [26] Swartz MA, Fleury ME (2007) Interstitial flow and its effects in soft tissues. Annu Rev Biomed Eng 9: 229-256. https://doi.org/10.1146/annurev.bioeng.9.060906.151850
    [27] Stader F, Liu C, Derbalah A, et al. (2024) A physiologically based pharmacokinetic model relates the subcutaneous bioavailability of monoclonal antibodies to the saturation of FcRn-mediated recycling in injection-site-draining lymph nodes. Antibodies (Basel) 13: 70. https://doi.org/10.3390/antib13030070
    [28] Wu F, Bhansali SG, Law WC, et al. (2012) Fluorescence imaging of the lymph node uptake of proteins in mice after subcutaneous injection: molecular weight dependence. Pharm Res 29: 1843-1853. https://doi.org/10.1007/s11095-012-0708-6
    [29] Zhong X, Liu Y, Ardekani AM (2024) A compartment model for subcutaneous injection of monoclonal antibodies. Int J Pharm 650: 123687. https://doi.org/10.1016/j.ijpharm.2023.123687
    [30] Datta-Mannan A, Estwick S, Zhou C, et al. (2020) Influence of physiochemical properties on the subcutaneous absorption and bioavailability of monoclonal antibodies. MAbs 12: 1770028. https://doi.org/10.1080/19420862.2020.1770028
    [31] Mieczkowski CA (2023) The evolution of commercial antibody formulations. J Pharm Sci 112: 1801-1810. https://doi.org/10.1016/j.xphs.2023.03.026
    [32] Kinderman F, Yerby B, Jawa V, et al. (2019) Impact of precipitation of antibody therapeutics after subcutaneous injection on pharmacokinetics and immunogenicity. J Pharm Sci 108: 1953-1963. https://doi.org/10.1016/j.xphs.2019.01.015
    [33] Kijanka G, Bee JS, Bishop SM, et al. (2016) Fate of multimeric oligomers, submicron, and micron size aggregates of monoclonal antibodies upon subcutaneous injection in mice. J Pharm Sci 105: 1693-1704. https://doi.org/10.1016/j.xphs.2016.02.034
    [34] Filipe V, Que I, Carpenter JF, et al. (2014) In vivo fluorescence imaging of IgG1 aggregates after subcutaneous and intravenous injection in mice. Pharm Res 31: 216-227. https://doi.org/10.1007/s11095-013-1154-9
    [35] Kijanka G, Prokopowicz M, Schellekens H, et al. (2014) Influence of aggregation and route of injection on the biodistribution of mouse serum albumin. Plos One 9: e85281. https://doi.org/10.1371/journal.pone.0085281
    [36] Wang W, Chen N, Shen X, et al. (2012) Lymphatic transport and catabolism of therapeutic proteins after subcutaneous administration to rats and dogs. Drug Metab Dispos 40: 952-962. https://doi.org/10.1124/dmd.111.043604
    [37] Thomas VA, Balthasar JP (2019) Understanding inter-individual variability in monoclonal antibody disposition. Antibodies (Basel) 8: 56. https://doi.org/10.3390/antib8040056
    [38] Richter WF, Bhansali SG, Morris ME (2012) Mechanistic determinants of biotherapeutics absorption following SC administration. AAPS J 14: 559-570. https://doi.org/10.1208/s12248-012-9367-0
    [39] Supersaxo A, Hein WR, Steffen H (1990) Effect of molecular weight on the lymphatic absorption of water-soluble compounds following subcutaneous administration. Pharm Res 7: 167-169. https://doi.org/10.1023/a:1015880819328
    [40] Yang TH, Cleland JL, Lam X, et al. (2000) Effect of zinc binding and precipitation on structures of recombinant human growth hormone and nerve growth factor. J Pharm Sci 89: 1480-1485. https://doi.org/10.1002/1520-6017(200011)89:11<1480::aid-jps10>3.0.co;2-m
    [41] Höybye C (2023) Comparing treatment with daily and long-acting growth hormone formulations in adults with growth hormone deficiency: challenging issues, benefits, and risks. Best Pract Res Clin Endocrinol Metab 37: 101788. https://doi.org/10.1016/j.beem.2023.101788
    [42] Cai Y, Xu M, Yuan M, et al. (2014) Developments in human growth hormone preparations: sustained-release, prolonged half-life, novel injection devices, and alternative delivery routes. Int J Nanomedicine 9: 3527-3538. https://doi.org/10.2147/IJN.S63507
    [43] FDA label, Eli Lilly and Company: Humatrope® somatropin (rDNA origin) for injection vials and cartridges (2005). Available from: https://www.accessdata.fda.gov/drugsatfda_docs/label/2006/019640s047,019640s052lbl.pdf
    [44] Jordan F, Naylor A, Kelly CA, et al. (2010) Sustained release hGH microsphere formulation produced by a novel supercritical fluid technology: in vivo studies. J Control Release 141: 153-160. https://doi.org/10.1016/j.jconrel.2009.09.013
    [45] Tracy MA (1998) Development and scale-up of a microsphere protein delivery system. Biotechnol Prog 14: 108-115. https://doi.org/10.1021/bp9701271
    [46] Park K, Skidmore S, Hadar J, et al. (2019) Injectable, long-acting PLGA formulations: analyzing PLGA and understanding microparticle formation. J Control Release 304: 125-134. https://doi.org/10.1016/j.jconrel.2019.05.003
    [47] Oe Y, Kobayashi M, Yoshida T, et al. (2024) Injectable testosterone PLGA microsphere with different characteristics: effect of preparation method (paddle mixing versus microfluidic device). Pharm Dev Technol 29: 482-491. https://doi.org/10.1080/10837450.2024.2348580
    [48] Kojima R, Yoshida T, Tasaki H, et al. (2015) Release mechanisms of tacrolimus-loaded PLGA and PLA microspheres and immunosuppressive effects of the microspheres in a rat heart transplantation model. Int J Pharm 492: 20-27. https://doi.org/10.1016/j.ijpharm.2015.07.004
    [49] van de Weert M, Hoechstetter J, Hennink WE, et al. (2000) The effect of a water/organic solvent interface on the structural stability of lysozyme. J Control Release 68: 351-359. https://doi.org/10.1016/s0168-3659(00)00277-7
    [50] Su Y, Zhang B, Sun R, et al. (2021) PLGA-based biodegradable microspheres in drug delivery: recent advances in research and application. Drug Deliv 28: 1397-1418. https://doi.org/10.1080/10717544.2021.1938756
    [51] FDA label, Genentech, Inc.: Nutropin Depot® somatropin (rDNA origin) for injectable suspension (1999). Available from: https://www.accessdata.fda.gov/drugsatfda_docs/label/2004/21075s008lbl.pdf
    [52] Kemp SF, Fielder PJ, Attie KM, et al. (2004) Pharmacokinetic and pharmacodynamic characteristics of a long-acting growth hormone (GH) preparation (nutropin depot) in GH-deficient children. J Clin Endocrinol Metab 89: 3234-3240. https://doi.org/10.1210/jc.2003-030825
    [53] Shive MS, Anderson JM (1997) Biodegradation and biocompatibility of PLA and PLGA microspheres. Adv Drug Deliv Rev 28: 5-24. https://doi.org/10.1016/s0169-409x(97)00048-3
    [54] Zhang H, Yang Z, Wu D, et al. (2023) The effect of polymer blends on the in vitro release/degradation and pharmacokinetics of moxidectin-loaded PLGA microspheres. Int J Mol Sci 24: 14729. https://doi.org/10.3390/ijms241914729
    [55] Shah VR, Gupta PK (2018) Structural stability of recombinant human growth hormone (r-hGH) as a function of polymer surface properties. Pharm Res 35: 98. https://doi.org/10.1007/s11095-018-2372-y
    [56] Bosquillon C, Préat V, Vanbever R (2004) Pulmonary delivery of growth hormone using dry powders and visualization of its local fate in rats. J Control Release 96: 233-244. https://doi.org/10.1016/j.jconrel.2004.01.027
    [57] Patton JS, McCabe JG, Hansen SE, et al. (1989) Absorption of human growth hormone from the rat lung. Biotechnol Ther 1: 213-228.
    [58] Shive MS, Anderson JM (1997) Biodegradation and biocompatibility of PLA and PLGA microspheres. Adv Drug Deliv Rev 28: 5-24. https://doi.org/10.1016/s0169-409x(97)00048-3
    [59] Ningrum RA (2014) Human interferon alpha-2b: a therapeutic protein for cancer treatment. Scientifica (Cairo) : 970315. https://doi.org/10.1155/2014/970315
    [60] Radwanski E, Perentesis G, Jacobs S, et al. (1987) Pharmacokinetics of interferon alpha-2b in healthy volunteers. J Clin Pharmacol 27: 432-435. https://doi.org/10.1002/j.1552-4604.1987.tb03044.x
    [61] Li Z, Li L, Liu Y, et al. (2011) Development of interferon alpha-2b microspheres with constant release. Int J Pharm 410: 48-53. https://doi.org/10.1016/j.ijpharm.2011.03.016
    [62] Chan Y-P, Meyrueix R, Kravtzoff R, et al. (2007) Review on Medusa®: a polymer-based sustained release technology for protein and peptide drugs. Expert Opin Drug Deliv 4: 441-451. https://doi.org/10.1517/17425247.4.4.441
    [63] Trépo C, Meyrueix R, Maynard M, et al. (2006) Novel sustained release formulation of IFNα-2b improves tolerability and demonstrates potent viral load reduction in a phase I/II HCV clinical trial. J Clin Virol 36: S24. https://doi.org/10.1016/S1386-6532(06)80081-8
    [64] Bonnet-Gonnet C, Chognot D, Soula O, et al. (2014) Pharmaceutical formulations for the prolonged release of active principle(s), and their applications, especially therapeutic applications. US Patent : 8679540 B2.
    [65] Hill CP, Osslund TD, Eisenberg D (1993) The structure of granulocyte-colony-stimulating factor and its relationship to other growth factors. Proc Natl Acad Sci USA 90: 5167-5171. https://doi.org/10.1073/pnas.90.11.5167
    [66] Nagabhushan TL, Reichert P, Walter MR, et al. (2011) Type I interferon structures: possible scaffolds for the interferon-alpha receptor complex. Can J Chem 80: 1166-1173. https://doi.org/10.1139/v02-158
    [67] Chino M, Maglio O, Nastri F, et al. (2015) Artificial diiron enzymes with a de novo designed four-helix bundle structure. Eur J Inorg Chem 21: 3371-3390. https://doi.org/10.1002/ejic.201500470
    [68] Schaefer MH, Wanker EE, Andrade-Navarro MA (2012) Evolution and function of CAG/polyglutamine repeats in protein-protein interaction networks. Nucleic Acids Res 40: 4273-4287. https://doi.org/10.1093/nar/gks011
    [69] Jakubek RS, Workman RJ, White SE, et al. (2019) Polyglutamine solution-state structural propensity is repeat length dependent. J Phys Chem B 123: 4193-4203. https://doi.org/10.1021/acs.jpcb.9b01433
    [70] Rathod S, Bahadur P, Tiwari S (2021) Nanocarriers based on vitamin E-TPGS: Design principle and molecular insights into improving the efficacy of anticancer drugs. Int J Pharm 592: 120045. https://doi.org/10.1016/j.ijpharm.2020.120045
    [71] Ellmerer M, Schaupp L, Brunner GA, et al. (2000) Measurement of interstitial albumin in human skeletal muscle and adipose tissue by open-flow microperfusion. Am J Physiol Endocrinol Metab 278: E352-356. https://doi.org/10.1152/ajpendo.2000.278.2.E352
    [72] Kaja S, Hilgenberg JD, Everett E, et al. (2011) Effects of dilution and prolonged storage with preservative in a polyethylene container on Bevacizumab (Avastin™) for topical delivery as a nasal spray in anti-hereditary hemorrhagic telangiectasia and related therapies. Hum Antibodies 20: 95-101. https://doi.org/10.3233/HAB-2011-0244
    [73] Elebiyo TC, Rotimi D, Evbuomwan IO, et al. (2022) Reassessing vascular endothelial growth factor (VEGF) in anti-angiogenic cancer therapy. Cancer Treat Res Commun 32: 100620. https://doi.org/10.1016/j.ctarc.2022.100620
    [74] Lu JF, Bruno R, Eppler S, et al. (2008) Clinical pharmacokinetics of bevacizumab in patients with solid tumors. Cancer Chemoth Pharm 62: 779-786. https://doi.org/10.1007/s00280-007-0664-8
    [75] Lee ALZ, Ng VWL, Gao S, et al. (2015) Injectable biodegradable hydrogels from vitamin D-functionalized polycarbonates for the delivery of avastin with enhanced therapeutic efficiency against metastatic colorectal cancer. Biomacromolecules 16: 465-475. https://doi.org/10.1021/bm5015206
    [76] Fletcher NA, Krebs MD (2018) Sustained delivery of anti-VEGF from injectable hydrogel systems provides a prolonged decrease of endothelial cell proliferation and angiogenesis in vitro. RSC Adv 8: 8999-9005. https://doi.org/10.1039/c7ra13014g
    [77] Courtenay AJ, McCrudden MTC, McAvoy KJ, et al. (2018) Microneedle-mediated transdermal delivery of bevacizumab. Mol Pharm 15: 3545-3556. https://doi.org/10.1021/acs.molpharmaceut.8b00544
    [78] Huynh V, Wylie RG (2019) Displacement affinity release of antibodies from injectable hydrogels. ACS Appl Mater Interfaces 11: 30648-30660. https://doi.org/10.1021/acsami.9b12572
    [79] Gregoritza M, Messmann V, Abstiens K, et al. (2017) Controlled antibody release from degradable thermoresponsive hydrogels cross-linked by Diels-Alder chemistry. Biomacromolecules 18: 2410-2418. https://doi.org/10.1021/acs.biomac.7b00587
    [80] Huynh V, Wylie RG (2018) Competitive affinity release for long-term delivery of antibodies from hydrogels. Angew Chem Int Ed Engl 57: 3406-3410. https://doi.org/10.1002/anie.201713428
    [81] Lin YS, Nguyen C, Mendoza JL, et al. (1999) Preclinical pharmacokinetics, interspecies scaling, and tissue distribution of a humanized monoclonal antibody against vascular endothelial growth factor. J Pharmacol Exp Ther 288: 371-378.
    [82] Lee ALZ, Ng VWL, Poon GL, et al. (2015) Co-delivery of antiviral and antifungal therapeutics for the treatment of sexually transmitted infections using a moldable, supramolecular hydrogel. Adv Healthc Mater 4: 385-394. https://doi.org/10.1002/adhm.201400340
    [83] Ghosh I, Gutka H, Krause ME, et al. (2023) A systematic review of commercial high concentration antibody drug products approved in the US: formulation composition, dosage form design and primary packaging considerations. MAbs 15: 2205540. https://doi.org/10.1080/19420862.2023.2205540
    [84] Yang C, Lee A, Gao S, et al. (2019) Hydrogels with prolonged release of therapeutic antibody: Block junction chemistry modification of ‘ABA’ copolymers provides superior anticancer efficacy. J Control Release 293: 193-200. https://doi.org/10.1016/j.jconrel.2018.11.026
    [85] Kyriakides TR, Kim HJ, Zheng C, et al. (2022) Foreign body response to synthetic polymer biomaterials and the role of adaptive immunity. Biomed Mater 17: 022007. https://doi.org/10.1088/1748-605X/ac5574
    [86] Challa DK, Wang X, Montoyo HP, et al. (2019) Neonatal Fc receptor expression in macrophages is indispensable for IgG homeostasis. MAbs 11: 848-860. https://doi.org/10.1080/19420862.2019.1602459
    [87] Stader F, Liu C, Derbalah A, et al. (2024) A physiologically based pharmacokinetic model relates the subcutaneous bioavailability of monoclonal antibodies to the saturation of FcRn-mediated recycling in injection-site-draining lymph nodes. Antibodies (Basel) 13: 70. https://doi.org/10.3390/antib13030070
    [88] Davis JD, Padros MB, Conrado DJ, et al. (2024) Subcutaneous administration of monoclonal antibodies: pharmacology, delivery, immunogenicity, and learnings from applications to clinical development. Clin Pharmacol Ther 115: 422-439. https://doi.org/10.1002/cpt.3150
    [89] Mould DR, Baumann A, Kuhlmann J, et al. (2007) Population pharmacokinetics-pharmacodynamics of alemtuzumab (Campath) in patients with chronic lymphocytic leukaemia and its link to treatment response. Br J Clin Pharmacol 64: 278-291. https://doi.org/10.1111/j.1365-2125.2007.02914.x
    [90] Gibbs JP, Doshi S, Kuchimanchi M, et al. (2017) Impact of target-mediated elimination on the dose and regimen of evolocumab, a human monoclonal antibody against proprotein convertase subtilisin/kexin type 9 (PCSK9). J Clin Pharmacol 57: 616-626. https://doi.org/10.1002/jcph.840
    [91] Rudnick SI, Lou J, Shaller CC, et al. (2011) Influence of affinity and antigen internalization on the uptake and penetration of anti-HER2 antibodies in solid tumors. Cancer Res 71: 2250-2259. https://doi.org/10.1158/0008-5472.CAN-10-2277
    [92] Finley SD, Dhar M, Popel AS (2013) Compartment model predicts VEGF secretion and investigates the effects of VEGF trap in tumor-bearing mice. Front Oncol 3: 196. https://doi.org/10.3389/fonc.2013.00196
    [93] Ng CM, Fielder PJ, Jin J, et al. (2016) Mechanism-based competitive binding model to investigate the effect of neonatal Fc receptor binding affinity on the pharmacokinetic of humanized anti-VEGF monoclonal IgG1 antibody in cynomolgus monkey. AAPS J 18: 948-959. https://doi.org/10.1208/s12248-016-9911-4
    [94] Keyes KA, Mann L, Sherman M, et al. (2004) LY317615 decreases plasma VEGF levels in human tumor xenograft-bearing mice. Cancer Chemother Pharmacol 53: 133-140. https://doi.org/10.1007/s00280-003-0713-x
    [95] van Bueren JJL, Bleeker WK, Bøgh HO, et al. (2006) Effect of target dynamics on pharmacokinetics of a novel therapeutic antibody against the epidermal growth factor receptor: implications for the mechanisms of action. Cancer Res 66: 7630-7638. https://doi.org/10.1158/0008-5472.CAN-05-4010
    [96] Schneider EL, Hearn BR, Pfaff SJ, et al. (2016) Approach for half-Life extension of small antibody fragments that does not affect tissue uptake. Bioconjug Chem 27: 2534-2539. https://doi.org/10.1021/acs.bioconjchem.6b00469
    [97] Ottiger M, Thiel MA, Feige U, et al. (2009) Efficient intraocular penetration of topical anti-TNF-alpha single-chain antibody (ESBA105) to anterior and posterior segment without penetration enhancer. Invest Ophthalmol Vis Sci 50: 779-786. https://doi.org/10.1167/iovs.08-2372
    [98] Muñoz-López P, Ribas-Aparicio RM, Becerra-Báez EI, et al. (2022) Single-chain fragment variable: recent progress in cancer diagnosis and therapy. Cancers (Basel) 14: 4206. https://doi.org/10.3390/cancers14174206
    [99] Furrer E, Berdugo M, Stella C, et al. (2009) Pharmacokinetics and posterior segment biodistribution of ESBA105, an anti-TNF-alpha single-chain antibody, upon topical administration to the rabbit eye. Invest Ophthalmol Vis Sci 50: 771-778. https://doi.org/10.1167/iovs.08-2370
    [100] Li Z, Krippendorff BF, Sharma S, et al. (2016) Influence of molecular size on tissue distribution of antibody fragments. mAbs 8: 113-119. https://doi.org/10.1080/19420862.2015.1111497
    [101] Knowles SM, Wu AM (2012) Advances in immuno-positron emission tomography: antibodies for molecular imaging in oncology. J Clin Oncol 30: 3884-3892. https://doi.org/10.1200/JCO.2012.42.4887
    [102] Sakai T, Matsunaga T, Yamamoto Y, et al. (2008) Design and fabrication of a high-strength hydrogel with ideally homogeneous network structure from tetrahedron-like macromonomers. Macromolecules 41: 5379-5384. https://doi.org/10.1021/ma800476x
    [103] Schneider EL, Henise J, Reid R, et al. (2016) Hydrogel drug delivery system using self-cleaving covalent linkers for once-a-week administration of exenatide. Bioconjug Chem 27: 1210-1215. https://doi.org/10.1021/acs.bioconjchem.5b00690
    [104] Santi DV, Schneider EL, Reid R, et al. (2012) Predictable and tunable half-life extension of therapeutic agents by controlled chemical release from macromolecular conjugates. Proc Natl Acad Sci U S A 109: 6211-6216. https://doi.org/10.1073/pnas.1117147109
    [105] Santi DV, Schneider EL, Ashley GW (2014) Macromolecular prodrug that provides the irinotecan (CPT-11) active-metabolite SN-38 with ultralong half-life, low C(max), and low glucuronide formation. J Med Chem 57: 2303-2314. https://doi.org/10.1021/jm401644v
    [106] Deb T, Tu J, Franzini RM (2021) Mechanisms and substituent effects of metal-free bioorthogonal reactions. Chem Rev 121: 6850-6914. https://doi.org/10.1021/acs.chemrev.0c01013
    [107] Klein G, Reymond JL (1998) An enantioselective fluorimetric assay for alcohol dehydrogenases using albumin-catalyzed beta-elimination of umbelliferone. Bioorg Med Chem Lett 8: 1113-1116. https://doi.org/10.1016/s0960-894x(98)00165-6
    [108] Tu J, Xu M, Parvez S, et al. (2018) Bioorthogonal removal of 3-isocyanopropyl groups enables the controlled release of fluorophores and drugs in vivo. J Am Chem Soc 140: 8410-8414. https://doi.org/10.1021/jacs.8b05093
    [109] Roller SG, Dieckhaus CM, Santos WL, et al. (2002) Interaction between human serum albumin and the felbamate metabolites 4-hydroxy-5-phenyl-[1],[3]oxazinan-2-one and 2-phenylpropenal. Chem Res Toxicol 15: 815-824. https://doi.org/10.1021/tx025509h
    [110] Xu M, Deb T, Tu J, et al. (2019) Tuning isonitrile/tetrazine chemistry for accelerated deprotection and formation of stable conjugates. J Org Chem 84: 15520-15529. https://doi.org/10.1021/acs.joc.9b02522
    [111] Sakai T, Fujiyabu T (2020) Control over swelling of injectable gel. Physics of Polymer Gels. Weinheim: Wiley-VCH 261-276. https://doi.org/10.1002/9783527346547.ch17
    [112] Li Z, Yu X, Li Y, et al. (2021) A two-pore physiologically based pharmacokinetic model to predict subcutaneously administered different-size antibody/antibody fragments. AAPS J 23: 62. https://doi.org/10.1208/s12248-021-00588-8
    [113] Richter WF, Christianson GJ, Frances N, et al. (2018) Hematopoietic cells as site of first-pass catabolism after subcutaneous dosing and contributors to systemic clearance of a monoclonal antibody in mice. mAbs 10: 803-813. https://doi.org/10.1080/19420862.2018.1458808
    [114] Hangasky JA, Chen W, Dubois SP, et al. (2022) A very long-acting IL-15: implications for the immunotherapy of cancer. J Immunother Cancer 10: e004104. https://doi.org/10.1136/jitc-2021-004104
    [115] Kirkby M, Hutton ARJ, Donnelly RF (2020) Microneedle mediated transdermal delivery of protein, peptide and antibody based therapeutics: current status and future considerations. Pharm Res 37: 117. https://doi.org/10.1007/s11095-020-02844-6
    [116] Zhao J, Xu G, Yao X, et al. (2022) Microneedle-based insulin transdermal delivery system: current status and translation challenges. Drug Deliv Transl Res 12: 2403-2427. https://doi.org/10.1007/s13346-021-01077-3
    [117] Zhang J, Li H, Albakr L, et al. (2023) Microneedle-enabled therapeutics delivery and biosensing in clinical trials. J Control Release 360: 687-704. https://doi.org/10.1016/j.jconrel.2023.07.023
    [118] McCrudden MTC, Alkilani AZ, McCrudden CM, et al. (2014) Design and physicochemical characterisation of novel dissolving polymeric microneedle arrays for transdermal delivery of high dose, low molecular weight drugs. J Control Release 180: 71-80. https://doi.org/10.1016/j.jconrel.2014.02.007
    [119] Duarah S, Sharma M, Wen J (2019) Recent advances in microneedle-based drug delivery: Special emphasis on its use in paediatric population. Eur J Pharm Biopharm 136: 48-69. https://doi.org/10.1016/j.ejpb.2019.01.005
    [120] Kashaninejad N, Munaz A, Moghadas H, et al. (2021) Microneedle arrays for sampling and sensing skin interstitial fluid. Chemosensors 9: 83. https://doi.org/10.3390/chemosensors9040083
    [121] Olatunji O, Das DB, Garland MJ, et al. (2013) Influence of array interspacing on the force required for successful microneedle skin penetration: theoretical and practical approaches. J Pharm Sci 102: 1209-1221. https://doi.org/10.1002/jps.23439
    [122] Pawlaczyk M, Lelonkiewicz M, Wieczorowski M (2013) Age-dependent biomechanical properties of the skin. Postepy Dermatol Alergol 30: 302-306. https://doi.org/10.5114/pdia.2013.38359
    [123] Sandby-Møller J, Poulsen T, Wulf HC (2003) Epidermal thickness at different body sites: relationship to age, gender, pigmentation, blood content, skin type and smoking habits. Acta Derm Venereol 83: 410-413. https://doi.org/10.1080/00015550310015419
    [124] Courtenay AJ, McCrudden MTC, McAvoy KJ, et al. (2018) Microneedle-mediated transdermal delivery of bevacizumab. Mol Pharm 15: 3545-3556. https://doi.org/10.1021/acs.molpharmaceut.8b00544
    [125] Amodwala S, Kumar P, Thakkar HP (2017) Statistically optimized fast dissolving microneedle transdermal patch of meloxicam: a patient friendly approach to manage arthritis. Eur J Pharm Sci 104: 114-123. https://doi.org/10.1016/j.ejps.2017.04.001
    [126] Hutton ARJ, Kirkby M, Bogaert TV, et al. (2024) Transdermal administration of nanobody molecules using hydrogel-forming microarray patch technology: a unique delivery approach. Macromol Mater Eng 309: 2400029. https://doi.org/10.1002/mame.202400029
    [127] Hirobe S, Susai R, Takeuchi H, et al. (2021) Characteristics of immune induction by transcutaneous vaccination using dissolving microneedle patches in mice. Int J Pharm 601: 120563. https://doi.org/10.1016/j.ijpharm.2021.120563
    [128] Kalluri H, Banga AK (2011) Formation and closure of microchannels in skin following microporation. Pharm Res 28: 82-94. https://doi.org/10.1007/s11095-010-0122-x
    [129] Jung EC, Maibach HI (2015) Animal models for percutaneous absorption. J Appl Toxicol 35: 1-10. https://doi.org/10.1002/jat.3004
    [130] Capt A, Luzy AP, Esdaile D, et al. (2007) Comparison of the human skin grafted onto nude mouse model with in vivo and in vitro models in the prediction of percutaneous penetration of three lipophilic pesticides. Regul Toxicol Pharmacol 47: 274-287. https://doi.org/10.1016/j.yrtph.2006.11.008
    [131] Scott RC, Dugard PH, Doss AW (1986) Permeability of abnormal rat skin. J Invest Dermatol 86: 201-207. https://doi.org/10.1111/1523-1747.ep12284280
    [132] Haq MI, Smith E, John DN, et al. (2009) Clinical administration of microneedles: skin puncture, pain and sensation. Biomed Microdevices 11: 35-47. https://doi.org/10.1007/s10544-008-9208-1
    [133] Al-Kasasbeh R, Brady AJ, Courtenay AJ, et al. (2020) Evaluation of the clinical impact of repeat application of hydrogel-forming microneedle array patches. Drug Deliv Transl Res 10: 690-705. https://doi.org/10.1007/s13346-020-00727-2
  • This article has been cited by:

    1. Albert W. Pilkington, Gregory C. Donohoe, Novruz G. Akhmedov, Timothy Ferrebee, Stephen J. Valentine, Justin Legleiter, Hydrogen Peroxide Modifies Aβ–Membrane Interactions with Implications for Aβ40 Aggregation, 2019, 58, 0006-2960, 2893, 10.1021/acs.biochem.9b00233
    2. Albert W. Pilkington, Jane Schupp, Morgan Nyman, Stephen J. Valentine, David M. Smith, Justin Legleiter, Acetylation of Aβ40 Alters Aggregation in the Presence and Absence of Lipid Membranes, 2020, 11, 1948-7193, 146, 10.1021/acschemneuro.9b00483
    3. Kristine L. Teppang, Qilin Zhao, Jerry Yang, Development of fluorophores for the detection of oligomeric aggregates of amyloidogenic proteins found in neurodegenerative diseases, 2023, 11, 2296-2646, 10.3389/fchem.2023.1343118
    4. Akane Iida-Adachi, Hideki Nabika, Changes in Adsorption, Aggregation, and Diffusion Nature of Amyloid β on a Lipid Membrane in an Open System, 2025, 0743-7463, 10.1021/acs.langmuir.4c03663
  • Reader Comments
  • © 2025 the Author(s), licensee AIMS Press. This is an open access article distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/4.0)
通讯作者: 陈斌, bchen63@163.com
  • 1. 

    沈阳化工大学材料科学与工程学院 沈阳 110142

  1. 本站搜索
  2. 百度学术搜索
  3. 万方数据库搜索
  4. CNKI搜索

Metrics

Article views(700) PDF downloads(32) Cited by(0)

Figures and Tables

Figures(6)  /  Tables(9)

Other Articles By Authors

/

DownLoad:  Full-Size Img  PowerPoint
Return
Return

Catalog