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Heuberger, L.; Palivan, C.G.; , .; Eggenberger, O. Synthetic Compartments for Biomedical Applications. Encyclopedia. Available online: https://encyclopedia.pub/entry/23669 (accessed on 10 May 2024).
Heuberger L, Palivan CG,  , Eggenberger O. Synthetic Compartments for Biomedical Applications. Encyclopedia. Available at: https://encyclopedia.pub/entry/23669. Accessed May 10, 2024.
Heuberger, Lukas, Cornelia G. Palivan,  , Olivia Eggenberger. "Synthetic Compartments for Biomedical Applications" Encyclopedia, https://encyclopedia.pub/entry/23669 (accessed May 10, 2024).
Heuberger, L., Palivan, C.G., , ., & Eggenberger, O. (2022, June 01). Synthetic Compartments for Biomedical Applications. In Encyclopedia. https://encyclopedia.pub/entry/23669
Heuberger, Lukas, et al. "Synthetic Compartments for Biomedical Applications." Encyclopedia. Web. 01 June, 2022.
Synthetic Compartments for Biomedical Applications
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This entry is adapted from the peer-reviewed paper 10.3390/ijms23105718

Nano- and micrometer-sized compartments composed of synthetic polymers are designed to mimic spatial and temporal divisions found in nature. Self-assembly of polymers into compartments such as polymersomes, giant unilamellar vesicles (GUVs), layer-by-layer (LbL) capsules, capsosomes, or polyion complex vesicles (PICsomes) allows for the separation of defined environments from the exterior. These compartments can be further engineered through the incorporation of (bio)molecules within the lumen or into the membrane, while the membrane can be decorated with functional moieties to produce catalytic compartments with defined structures and functions. Nanometer-sized compartments are used for imaging, theranostic, and therapeutic applications as a more mechanically stable alternative to liposomes, and through the encapsulation of catalytic molecules, i.e., enzymes, catalytic compartments can localize and act in vivo. On the micrometer scale, such biohybrid systems are used to encapsulate model proteins and form multicompartmentalized structures through the combination of multiple compartments, reaching closer to the creation of artificial organelles and cells.

polymers compartments biomedical

1. Introduction

Mimicking the structure and function of materials found in nature is a well-known strategy for developing materials with structures and functions of interest. Vesicles are nature’s simplest compartments (e.g., organelles inside cells) and have existed since the first cells. While cell membranes are based on phospholipids, as they are natural amphiphiles, vesicle-forming molecules can also be synthetic. Copolymers are alternative amphiphiles that self-assemble into macromolecular assemblies [1][2]. Block copolymers, containing hydrophilic and hydrophobic regions that can be arranged in different repeating orders, have properties that can be controlled through chemical modification to support a desired application [3]. Based on the number of blocks used, amphiphilic polymers are referred to as di- or triblock copolymers, AB or ABA, respectively, with A representing the hydrophilic and B the hydrophobic block. Polyelectrolytes, polymers containing ionic or ionizable groups, also have the ability to self-assemble into synthetic compartments such as layer-by-layer (LbL) capsules or PICsomes [4]. Various molecular properties of the polymer blocks such as polydispersity, charge, block ratio and length, and molecular weight are essential to induce the supramolecular assemblies formed thereof. The addition of biomolecules changes the properties of the polymer membranes, the integration of phospholipids can change membrane mechanical properties [5][6][7], and membrane proteins can alter membrane permeability [8] and even provide the desired functionality via their intrinsic bioactivity [9][10].

2. Generation of Synthetic Compartments

A hollow cavity surrounded by a synthetic barrier (membrane, layers of polymers) represents the common architecture that forms single compartments. When more complex structures are the aim, there are two different approaches: (i) encapsulation of small nanocompartments in GUVs to generate compartments-in-compartments and (ii) zipping together compartments to generate clusters or networks [11][12][13][14].
Self-assembly of amphiphilic block copolymers in aqueous solutions can result in several types of nano- or micrometer-sized structures such as micelles, tubes, or vesicles (polymersomes and GUVs) [15][16]. Self-assembly is driven by noncovalent interactions such as the hydrophobic effect or electrostatic interactions [17]. A list of polymers commonly utilized to form compartments with a hollow-sphere architecture is presented in Table 1.
Here the researchers present the most established self-assembly methods for nano- and micro-sized polymer vesicles (Scheme 1) and briefly describe how layer-by-layer assembly is used to generate capsules and capsosomes. In methods such as solvent switch, the block copolymer is dissolved in a water-miscible organic solvent. This is followed by the dropwise addition of an aqueous buffer to slowly replace the organic phase [18][19]. Contrarily, the cosolvent method is based on the dropwise addition of a copolymer solution to an aqueous buffer phase, which induces the self-assembly process of copolymers [20]. One drawback of these methods is the residual presence of organic solvent in the final solution, which is undesirable for biologically relevant applications. The film rehydration method (Scheme 1A) takes place in a more biocompatible manner, as the organic solution of the copolymer is completely dried, forming a film. The thin copolymer film is subsequently rehydrated with an aqueous solution, inducing the self-assembly process and resulting in supramolecular architectures (micelles, polymersomes, worm-like assemblies). When the hydrophilic–hydrophobic ratio f of the copolymers is in the range of 35 ± 10% [21], vesicles are the favored supramolecular assembly, even if the copolymers have a rather high polydispersity index (PDI) [13][22]. Film rehydration is well suited for loading polymersomes with sensitive molecules, such as enzymes and proteins, during the self-assembly process [23]. However, as this process is based on statistic loading of the desired molecules present in the rehydration solution, the encapsulation efficiency is highly dependent on their solubility and usually ranges between 5 and 20% for encapsulation of a single type of high-molecular-weight molecule, such as proteins and enzymes, and decreases even further for coencapsulation of two types of proteins [24][25][26].
Ijms 23 05718 sch001 550
Scheme 1. Schematic representation of selected production methods of synthetic compartments: (A) film rehydration and subsequent extrusion of block copolymers; (B) electroformation; (C) double emulsion formation with a microfluidic setup; (D) polymerization-induced self-assembly (PISA); (E) layer-by-layer (LbL) assembly; (F) assembly of capsosomes; and (G) PICsomes.
When the aim is giant unilamellar vesicles, methods used for polymersome generation are joined by other methods, including electroformation. The electroformation technique (Scheme 1B) is based on the spontaneous swelling of a dried block copolymer film that has been deposited on two electrodes of indium tin oxide (ITO)-coated glass or platinum and the consequent formation of GUVs in the presence of an aqueous solution stimulated by an electric field [13][27]. This method has a high yield of assemblies with high levels of unilamellarity [28] but is limited by a broad size dispersity and can be used only for uncharged amphiphiles to avoid electrostatic interactions affecting the self-assembly process [29]. Emulsion centrifugation is a method for the formation of GUVs wherein a water-in-oil emulsion suspension is transferred into a water phase by centrifugation [30]. The single emulsions cross a polymer monolayer at the water/oil interface and are coated by a second monolayer, resulting in a bilayered GUV. Microfluidic technology represents a step forward that has been recently used for high-throughput GUV formation with a narrow size distribution based on microdevice channel sizes and junction design [30][31][32]. Polymer-stabilized water–oil–water (w/o/w) double emulsions are used to form GUVs. An aqueous solution is enclosed in a layer of organic phase, consisting of the amphiphilic block copolymer dissolved in a volatile organic solvent (Scheme 1C). A flow of outer aqueous solution then pinches off the double emulsion droplets. Double emulsions can be created with a multitude of different microfluidic designs, such as glass capillaries [32][33] or molded microchannels in varying layouts [34][35][36]. Subsequent evaporation of the volatile organic solvent leads to the formation of a GUV with a polymer membrane. An extremely high encapsulation efficiency (99%) can be obtained by including in the inner flow the molecules (enzymes, proteins) desired to be encapsulated within the generated GUVs. The molecules planned to be entrapped in the membrane (biopores, membrane proteins) are also included in the aqueous flow at this stage [35]. Despite the high encapsulation efficiency and monodispersity, there are still limitations to using this method for GUV formation, such as its complexity and the necessity of specialized equipment.
An entirely different approach is that of polymerization-induced self-assembly (PISA), a technique that directly produces nanoassemblies during the block copolymer synthesis (Scheme 1D) [37][38][39]. PISA’s principle is based on the chain extension of a soluble precursor polymer block in a suitable solvent with the simultaneous use of a second polymerizing monomer, resulting in the formation of an insoluble second block, yielding polymersomes [37][38][39]. The advantage of the method is its efficiency, as it combines synthesis with self-assembly and is characterized by monodispersity. On the other hand, this method is limited by decreased colloidal stability in the presence of ionic surfactants. Furthermore, PISA can only be applied for a small selection of monomers [40].
Polymer capsules are frequently formed through LbL deposition (Scheme 1E), a technique that involves the controlled adsorption of polymer layers on a sacrificial colloidal particle, alternating between oppositely charged materials, i.e., one layer of negatively charged polymer is followed by one of positively charged polymer [41][42][43]. Once the appropriate number of layers has been applied, the system is submerged in a solution designed to either dissolve the template or simply detach the vesicle membrane, allowing one to separate out the freshly formed vesicles. LbL capsule formation is simple yet versatile in terms of compartment size and components, including their functionality possibilities [44][45]. However, this method is limited by its dependence on the sacrificial template. Formed through a similar technique, capsosomes are capsules of which the membranes are composed of smaller vesicles. Their fabrication involves the deposition of an initial number of polymer layers onto a colloidal particle of specified size. Next, one or multiple layers of liposomes are attached, segregated by a polymeric separation layer, followed by a final deposition of several protective polymer layers (Scheme 1F) [46][47]. Assemblies of a different type, PICsomes, are the vesicular form of polyion complex (PIC) particles and are self-assembled through electrostatic interactions [19][22]. PICsomes are composed of oppositely charged block copolymers (Scheme 1G), and their membranes are semipermeable, especially to hydrophilic solutes. A major advantage of PICsomes is their facile formation—they naturally self-assemble through the mixing of their charged components [48]. One disadvantage of PICsomes is that their components typically need to be combined at equal concentrations to result in a charge-neutral vesicle, though recent experimentation has shown that charge-balance-sensitive materials can be formed by varying this ratio [49].
Table 1. Polymers used for biomedical applications.

Polymer

Method of Self-Assembly

Characteristics

Carbohydrate-b-PPG

Direct hydration method [50]

Forms capsosomes, inherently permeable to low-molecular-weight compounds

Chitosan

Sonication-assisted mixing (capsules) [51], LbL [52]

Biocompatible, natural polymer

CTAB

LbL [52]

Surfactant, forms micelles in the absence of another polymer

PA/DEX

LbL [53]

Biocompatible polysaccharide (anionic)

P(OEGMA300-grad-HPMA)

PISA [39]

Biocompatible assembly, monomers and a macromolecular precursor need to be: (i) solvophilic and (ii) compatible with each other

PA/PLA

LbL [53]

Biocompatible cationic polyelectrolyte

PAA

LbL [54]

Anionic polyelectrolyte

PAH

LbL [55][56]

Cationic polyelectrolyte

PAMAM

Mixing (PICsomes) [57]

Dendrimer (branched structure)

P(Asp-AP)

Mixing (PICsomes) [58][59][60]

Anionic polyelectrolyte, forms PICsomes, cannot form vesicles on its own

PATK

Mixing (PICsomes) [61]

Cationic polyelectrolyte

PBd-b-PEG

Double emulsion microfluidics [33]

Biocompatible

PBd–b-PEO

Emulsion centrifugation [30],

Electroformation [62],

Film rehydration [63]

Pure or as hybrid (with POPC) polymersomes for membrane protein insertion, assembly of asymmetric polymer/lipid (POPC) hybrid membranes

PBO-b-PG

Microfluidic double emulsion, solvent switch [64]

Biocompatible

PCL-b-P[Glu-stat-(Glu-ADA)]

Solvent switch [65]

Biodegradable, bone-targeting

PCL-b-PTrp-b-P(Lys-statPhe)

Solvent switch [66]

Biocompatible, biodegradable, antibacterial

PDMS-b-heparin

Film rehydration [67]

Forms polymersomes in combination with PMOXA-b-PDMS-b-PMOXA, forms micelles by itself

PDMS-g-PEO

Electroformation,

Film rehydration [68]

Pure or as hybrid (with PC) polymersomes and GUVs for membrane protein insertion

PEG-b-PCL

Electroformation [69], film rehydration [70]

Multidomain membrane formation with lipids (DPPC)

PEG-P(CLgTMC)

Direct hydration method [71]

Biodegradable, intrinsic fluorescence

PEG-b-P(CPTKMA-co-PEMA)

Solvent exchange method [72]

Biocompatible, conjugated with campthothecin

PEG-GPLGVRG-PCL-PGPMA

Film hydration method [73]

Biocompatible, MMP-cleavable peptide and CPP-mimicking polymer

PEG-b-PHPMA

PISA [74]

Highly hydrated membrane, size-selective transport of molecules

PEG-b-PIC

Solvent exchange [75]

Biocompatible, iodine-rich for SPECT/CT and radioisotope therapy

PEG-b-PLA

Film rehydration [70], double emulsion microfluidics [33]

Forms polymersomes with and without lipid mixing, biodegradable

PEG-b-polypeptide

Mixing (PICsomes) [76]

pH-responsive, biocompatible

PEG-b-PAsp

Mixing (PICsomes) [58][60]

Linear polymer, forms PICsomes, micelles or hydrogels, biocompatible

PEG-b-PS

Solvent switch method [77][78]

Biocompatible, formation of stomatocytes, rigid assemblies

PEI-b-PDLLA

Microfluidic double emulsion [79]

Biocompatible, cationic assemblies,

can form polymer stomatocytes

PEO-b-PBO

Film rehydration [80]

Forms asymmetric polymersomes

PEO-b-PCL

Emulsification-induced assembly [81]

Low interfacial tension solvent or SDS is needed to control the assembly

PEO-b-PCL-b-PMOXA

Film rehydration [82]

Rehydration at 62 °C due to the semi crystalline nature of the PCL block

PEO-b-P(CMA-stat-DEA-stat-GEMA)

Solvent exchange method [83]

Biocompatible, CMA photocrosslinking stabilization

PEO-b-PEHOx-b-PEtOz

Solvent switch, film rehydration [22]

Asymmetric membrane, can be used for directed protein insertion

PEO-b-PPO-b-PEO

(Pluronics L121)

Double emulsion microfluidics [33]

Assembly via DNA linkage

PiB-b-PEG

Freeze–thaw extrusion [84]

Biocompatible, high chemical and thermal stability

PLys

Mixing (PICsomes) [85]

Cationic polyelectrolyte

PMA

LbL [56]

Labor-intensive LbL assembly

PMOXA-b-PDMS

Film rehydration [86][87],

microfluidic double emulsion [35]

Formation of nano- and micro-sized vesicles in biocompatible, aqueous conditions, various channels and proteins can be inserted

PMOXA-b-PDMS-b-PMOXA

Film rehydration [67][88]

Formation of nano and micro-sized vesicles in biocompatible, aqueous conditions, various channels and proteins can be inserted

PMPC-b-PDPA

Film rehydration [80][89]

Formation of (asymmetric) polymersomes, can be electroporated

POEGMA-b-P(ST-co-VBA)

PISA [37]

Biocompatible assembly,

monomers and a macromolecular precursor need to be: (i) solvophilic and (ii) compatible with each other

Poly(dopamine)

LbL [90]

Simplified LbL capsule formation

PS-b-PEO

Emulsification [91]

High capacity of ammonia capture in bile salt-containing buffer

PSMA-PBzMA

PISA [38]

Biocompatible assembly,

monomers and a macromolecular precursor need to be: (i) solvophilic and (ii) compatible with each other

PSS-b-PEO-b-PSS

Mixing (PICsomes) [57]

Forms PICsomes with loops within the membrane when combined with poly(amidoamine) dendrimers

PVP

LbL [92]

Work-intensive LbL assembly

3. Requirements for Compartments to Be Used in Biomedical Applications

For any biologically relevant material, the transition from the research laboratory to a clinical setting is a complex procedure. This is particularly true when the final application is in the field of medicine, pharmaceutical production, or personal care [93][94][95]. In the case of compartments, there is a complex set of requirements, first for the copolymers used to generate the compartments and then for the compartments themselves. Therefore, for an amphiphilic block copolymer or a polyelectrolyte to be used in biomedical applications some crucial aspects need to be considered: (i) the polymers should be able to self-assemble in aqueous solutions [15][19][82]; (ii) they need to be nontoxic and biocompatible [96]; (iii) they need to have the appropriate physical characteristics (i.e., flexibility, membrane thickness) [97] in order to facilitate the functional insertion, encapsulation, and reconstitution of biomolecules [98][99]; (iv) control over their surface charge is crucial for the attachment of biomolecules or further in vivo applications [100]; (v) they need to maintain stability under physiological conditions [101][102] (i.e., in high temperature or salt concentration, their functionality must remain, and the availability of the encapsulated biomolecules must be sustained); and (vi) of particular import for therapeutic compartments is their ability to undergo endosomal escape so the therapeutic agent is not hindered by cells’ defense mechanisms and can arrive at the pathogenic site [103][104][105]. Besides these, one of the most limiting factors is the fate of copolymers in the body. Therefore, their biodegradability still remains a real challenge for various copolymers that fulfill the complex list of factors aforementioned.
Second, the compartments planned to be used in medical applications should fulfill their own set of requirements. While polymersomes, capsules, and capsosomes should preserve their integrity and act as catalytic compartments, they must also allow the molecular flow of substrates and products. Their membrane can be rendered permeable by biopores such as ion channels [98][106], peptide pores [26][107], DNA nanopores [89], and natural membrane proteins [102]. While many examples of functional protein reconstitution in polymeric membranes have been shown, the increased hydrophobic mismatch of polymeric membranes as compared with lipidic ones limits the choice of membrane protein. High membrane fluidity is essential for protein incorporation, as it allows integrating proteins into membranes that are several times thicker than the protein itself and helps the protein to overcome the size mismatch between its own hydrophobic region and the hydrophobic region of the polymer membrane [97]. Furthermore, the surface charge plays a crucial role in the in vivo functionality, biodistribution, and cellular uptake of the systems [108][109]. Specifically, positively charged compartments have been found to be better uptaken by cells and exhibit improved biodistribution [110][111][112], while negatively charged ones are usually less toxic and better at specific tissue targeting [112][113][114].
The surface functionalization of polymersomes, capsules, and capsosomes opens up many possibilities for the assembly of complex soft compartments. However, the attachment of functional groups changes the overall charge and might induce interactions with the environment or trigger aggregation, increasing the intrinsic toxicity. Additionally, the formation of clusters of compartments increases the size of the final assembly. This limits the possible applications mainly to the intercellular matrix [115][116]. Overall, use in medical applications requires both the polymer properties (e.g., toxicity, biocompatibility) and those of the compartment (e.g., membrane composition, functionalization, size, charge) to be carefully tailored.

4. Applications of Compartments in the Biomedical Field

Numerous studies have investigated the benefits and limitations of nanometer-sized compartments for their use in imaging, therapeutics, and theranostics. As a first step, in vitro studies have explored the activity and cytotoxicity of the systems for these applications, while in vivo studies have highlighted their suitability and investigate in-depth parameters for clinical translation. Meanwhile, micrometer-sized vesicles have facilitated the modeling of cells, a crucial step in bottom-up synthetic biology aiming to bring further insights to real-life processes. An overview of biomolecules that have been used within compartments or in their membranes is presented in Table 2.
Table 2. Biomolecules and their applications in compartments.

Biomolecule

Polymer

Location in Assembly

Application/Function

Actin

PMOXA-b-PDMS-b-PMOXA [67]

Encapsulated (in GUVs)

Polymerization to form a cytoskeleton

ATP synthase

PDMS-g-PEO, PBd-b-PEO [68][117]

Incorporated within membrane (GUVs)

ATP generation

Bacteriorhodopsin

PDMS-g-PEO, PBd- b-PEO [117]

Incorporated within membrane (GUVs)

Pumping protons across membrane

Catalase

PEG-b-PS [78], PAH and DEX [55]

Encapsulated with the stomata of polymer stomatocytes and LbL capsules

Conversion of hydrogen peroxide to oxygen and water for self-propelled movement

Cholesterol–DNA

PEO-b-PPO-b-PEO (Pluronics L121), PBd-b-PEG, PLA-b-PEG [33]

Incorporated within membrane (GUVs)

Clustering of polymersomes

Cytochrome bo3 ubiquinol oxidase (Cyt bo3)

PBd–PEO:POPC hybrid [118], PDMS-g-PEO and PDMS-g-PEO/PC hybrid [68][119]

Incorporated within membrane (polymersomes, GUVs)

Pumping protons across membrane

DNA nanopore NP-3c

PMPC-b-PDPA [89]

Incorporated within membrane (GUVs)

Pore formation for cross-membrane diffusion

Dopa decarboxylase (DDC)

PMOXA-b-PDMS [120]

Encapsulated (in polymersomes)

Production of dopamine

Erythrosine B (and its ester derivatives)

F127 Pluronic (mixed with DPPC lipids) [121]

Incorporated within membrane (polymersomes)

Photodynamic therapy

Glucose oxidase (Gox)

PMOXA-b-PDMS [35][87], PEG-b-P(CPTKMA-co-PEMA) [72], PATK and PEG-b-Pasp [61]

Encapsulated (in GUVs, polymersomes, and PICsomes)

Catalysis of glucose oxidation to hydrogen peroxide and D-glucono-δ-lactone

Gramicidin

PMOXA-b-PDMS [35], PMOXA-b-PDMS-b-PMOXA [67]

Incorporated within membrane

Membrane permeabilization towards ions

Horseradish peroxidase (HRP)

PMOXA-b-PDMS [35], PMOXA-b-PDMS-b-PMOXA [86][101],

carbohydrate-b-PPG [50]

Encapsulated (in GUVs, polymersomes, capsosomes)

Catalysis of oxidation of organic substrates by hydrogen peroxide

Icosane

PAA and PAH (LbL) [54]

Encapsulated (in capsules)

Acting as a phase change material for thermal energy storage

Inducible nitric oxide synthase (iNOS)

PMOXA-b-PDMS-b-PMOXA [122]

Encapsulated (in polymersomes)

Oxidation of l-arginine to l-citrulline and nitric oxide (NO)

Ionomycin

PMOXA-b-PDMS-b-PMOXA [67]

Incorporated within membrane

Membrane permeabilization towards ions

Laccase

PMOXA-b-PDMS [123]

Encapsulated (in polymersomes)

Oxidation of phenolic and nonphenolic compounds

Lactoperoxidase (LPO)

PMOXA-b-PDMS [87]

Encapsulated (in polymersomes)

Oxidation of Amplex red using hydrogen peroxide

L-asparaginase

PMPC-b-PDPA and PEO-b-PBO [80], PEG-b-Pasp and P(Asp-AP) [60],

PEG-b-PHPMA [74]

Encapsulated (in polymersomes, PICsomes)

Catalysis of L-asparagine to l-aspartic acid and ammonia

Lipase

PMOXA-b-PDMS-b-PMOXA [67]

Encapsulated (in polymersomes)

Catalysis of the hydrolysis of fats

Luciferase

PMOXA-b-PDMS [124]

Encapsulated (in polymersomes)

Bioluminescence

Melittin

PMOXA-b-PDMS [87][107][125]

Incorporated within membrane (polymersomes, GUVs)

Pore formation for cross-membrane diffusion

Methionine γ-lyase (MGL)

PEG-P(Asp) and PLys [59][85]

Encapsulated (in PICsomes)

Cancer therapy

Outer membrane protein F from E. coli (OmpF)

PMOXA-b-PDMS [35], PMOXA-b-PDMS-b-PMOXA [86][101]

Incorporated within membrane (GUVs, polymersomes)

Pore formation for cross-membrane diffusion

Penicillin acylase

PMOXA-b-PDMS-b-PMOXA [126]

Encapsulated (in polymersomes)

Production of antibiotic cephalexin

Rnase H

PEG-b-polypeptide (with single-stranded oligonucleotides) [76]

Encapsulated (in PICsomes)

Gene knockout therapy

β-galactosidase

PMOXA-b-PDMS [35]

carbohydrate-b-PPG [50]

Encapsulated (in GUVs, capsosomes)

Catalysis of the hydrolysis of β-galactosides into monosaccharides

β-glucuronidase

PMOXA-b-PDMS [125]

Encapsulated (in polymersomes)

Cleavage of the glucuronide moiety from glucuronide-conjugates

Soluble guanylyl cyclase (sGC)

PMOXA-b-PDMS-b-PMOXA [122]

Encapsulated (in polymersomes)

Production of cyclic 3,5-guanosine monophosphate (cGMP)

Trypsin

PMPC-b-PDPA [89]

Encapsulated (in polymersomes)

Hydrolyzation of proteins

Tyrosinase

PMOXA-b-PDMS [127]

Encapsulated (in polymersomes)

Oxidation of L-DOPA

Urate oxidase (UOX)

PMOXA-b-PDMS-b-PMOXA [12]

Encapsulated (in polymersomes)

Production of hydrogen peroxide for a cascade reaction

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Subjects: Polymer Science
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Lukas Heuberger
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Cornelia G. Palivan
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Olivia Eggenberger
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Update Date: 02 Jun 2022
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