Lipid Nanoparticle Co-Encapsulation: Design Strategies for Multiple Payloads

When Should Multiple Payloads Be Co-Encapsulated in the Same LNP?

Co-encapsulating multiple active components into a single lipid nanoparticle is a deliberate design decision, not a default option. The formulation overhead of co-loading two chemically or biologically distinct payloads is substantial — additional optimization of lipid composition, charge ratio, loading sequence, and analytical workflow is unavoidable — so the question every project team must answer first is whether the biological problem genuinely requires both payloads to be delivered to the same cell at the same time, or whether two separately administered LNPs would suffice.

The strongest case for co-encapsulation arises when two components must reach the same cell, in a defined stoichiometry, to produce a meaningful biological effect. Classic examples include multi-antigen vaccines where simultaneous presentation shapes the immune response, dual-nucleic-acid systems where mRNA expression and siRNA-mediated knockdown must occur in the same cellular compartment, and gene-editing cargoes where editor protein, guide RNA, and donor DNA must all access the same nucleus. Outside these scenarios — for example, when two drugs act on different cell populations or when one payload is dominant and the other is supportive — separate delivery is usually simpler, more controllable, and easier to characterize.

Once a project confirms that co-encapsulation is justified, co-encapsulation of multiple payloads in LNPs becomes the central technical focus. The remainder of this resource examines the seven most common co-encapsulation scenarios encountered in LNP drug discovery, the design variables that determine success in each, and the engineering issues that frequently decide whether a co-loaded formulation ultimately works.

Co-Encapsulation of Multiple mRNAs

Co-loading two or more mRNAs into a single LNP is the simplest multi-nucleic-acid case, because every cargo shares the same anionic phosphate chemistry and partitions into the ionizable lipid core through the same electrostatic mechanism. The resulting particle is essentially a single-payload LNP in which the payload is a defined mRNA mixture.

Key Considerations: Transcript Length, Stability, and Protein Expression Ratios

Three variables determine whether a multi-mRNA LNP delivers proteins in the intended ratios:

• Transcript length affects loading efficiency: Shorter mRNAs incorporate into the ionizable lipid core more efficiently per microgram than longer transcripts, which can shift the effective expression ratio away from the input mass ratio if length differences are large.
• Per-mRNA chemical stability differs: Modified nucleoside content, cap structure, and poly(A) tail design affect how each transcript withstands storage and handling; the least stable component typically dictates the usable shelf life of the co-loaded product.
• Translation rates vary between constructs: Codon usage, UTR design, and protein turnover kinetics all influence the protein output per mRNA molecule, so the desired protein expression ratio is rarely identical to the input mRNA mass ratio.

LNP Design: Balancing Total RNA Loading and Individual mRNA Content

For lipid nanoparticles used in mRNA delivery, the design variables that matter most are total RNA-to-lipid mass ratio, N/P ratio, and the relative input mass of each transcript. Total RNA load controls encapsulation efficiency at the bulk level: if the load is too high, both transcripts compete for ionizable lipid and partial loading of each results; if too low, particle stability and endosomal escape efficiency may degrade. The input ratio between mRNAs is the most flexible variable, because protein expression scales approximately linearly with input mRNA mass within the optimized range. Adjusting input ratios is therefore the fastest way to compensate for length- or stability-driven biases observed in early expression data.

Encapsulation Strategies: Premixing mRNAs and Optimizing Input Ratios

The standard encapsulation strategy is to pre-mix the two mRNAs in the aqueous phase at the desired mass ratio, then combine with the lipid-ethanol phase through standard microfluidic mixing. Because both mRNAs are negatively charged and have similar ionizable-lipid affinity, premixing usually gives a co-encapsulation efficiency very close to that of a single-mRNA control. The main process risk is aggregation at very high total mRNA concentration, which can be mitigated by reducing total RNA load, increasing post-mixing dilution, or screening alternative ionizable lipids with higher loading capacity.

Table 1. Multiple mRNA Co-Encapsulation Design Summary.

Co-Encapsulation of Multiple siRNAs

Co-encapsulating multiple siRNAs in one LNP is common in target-validation studies and in combinational gene-silencing therapeutics that aim to suppress redundant or compensatory pathways. Each siRNA duplex is short, chemically uniform, and anionic, so the loading behavior resembles that of mRNA in many respects — but the relevant downstream readout is silencing efficiency rather than translation.

Key Considerations: Individual siRNA Potency and Combined Silencing Goals

The design of a multi-siRNA LNP must respect the biology of silencing rather than the biology of translation:

• Per-siRNA potency is the dominant variable: siRNAs differ widely in intrinsic silencing activity at the same dose, so equal-mass input does not guarantee equal knockdown. The more potent duplex should be loaded at a lower ratio than the less potent one.
• Off-target effects scale with siRNA dose: Combining three or four siRNAs increases the cumulative off-target burden, which constrains the maximum useful total siRNA load per particle.
• Functional target overlap must be evaluated: Two siRNAs against redundant isoforms or parallel pathway members only make sense if their combined knockdown produces a phenotype neither achieves alone.

LNP Design: Balancing siRNA Doses and Lipid-to-RNA Ratios

For lipid nanoparticles used in siRNA delivery, lipid-to-siRNA mass ratios typically fall in the range of 10:1 to 25:1, which is somewhat higher than the ratios used for longer mRNA because the shorter duplex has lower charge density per microgram and benefits from a higher ionizable-lipid share. Higher PEG-lipid content (1.5-3 mol%) is often used to compensate for the reduced colloidal stability that accompanies the lower overall RNA load, and the ionizable lipid pK_a is tuned slightly more toward 6.0-6.4 to match the endosomal escape window expected for siRNA-loaded particles.

Encapsulation Strategies: Mixed-siRNA Loading and Payload-Specific Recovery Control

Standard siRNA co-encapsulation uses a pre-mixed siRNA pool in the aqueous phase at the chosen input ratio, with single-step microfluidic mixing. Because siRNA is short and chemically uniform, co-loading is rarely the technical bottleneck. The harder problem is the post-encapsulation analytical workflow: each siRNA in the mixture must be quantified individually, which is achievable by HPLC or by duplex-specific probes, and free siRNA must be removed without preferential loss of any individual component. Tangential flow filtration (TFF) with appropriately chosen molecular-weight cutoffs preserves all siRNAs equally and is the standard polishing step.

Table 2. Multiple siRNA Co-Encapsulation Design Summary.

Co-Encapsulation of mRNA and siRNA

Co-encapsulation of an mRNA and an siRNA in the same particle is technically more demanding than either cargo alone: the two species differ by roughly two orders of magnitude in molecular weight, have different per-microgram charge densities, and compete for the same ionizable lipid pool. Yet this combination is increasingly attractive for therapeutic strategies requiring simultaneous expression of a therapeutic protein and suppression of a competing or resistance-driving endogenous transcript.

Key Considerations: RNA Size Differences and Expression-Silencing Timing

Two distinct challenges shape the design of an mRNA-plus-siRNA LNP:

• Size disparity shifts the effective input ratio: Because siRNA carries far more phosphate per microgram than long mRNA, equivalent mass inputs do not correspond to equivalent charge inputs, and the ionizable lipid pool is depleted preferentially by whichever species dominates the charge calculation.
• Functional timing must be coordinated: siRNA engages the RISC machinery within hours of delivery, while mRNA-driven protein expression takes longer to reach functional levels. If the siRNA is meant to suppress a transcript that the mRNA-encoded protein would otherwise induce, the timing gap is part of the design.
• Endosomal escape must satisfy both cargos: A particle optimized only for mRNA expression may still release siRNA poorly into the cytosol where RISC resides, and vice versa.

LNP Design: Balancing RNA Association, Protection, and Intracellular Availability

For lipid nanoparticles used in RNA delivery across both mRNA and siRNA, the practical design compromise is to use a moderately higher N/P ratio (6-9) than for mRNA-only formulations, and to choose an ionizable lipid with pK_a in the 6.2-6.5 range that supports endosomal escape across a broad dose range. PEG-lipid content is held at 1.5-2.5 mol% with a C14 anchor to balance colloidal stability during storage against rapid cell-interactive exposure after administration. Helper-lipid selection (DSPC versus DOPE) shifts the bilayer toward either the lamellar or the hexagonal phase, which in turn favors the release of one cargo type over the other.

Encapsulation Strategies: Optimizing RNA Ratios and Mixing Conditions

The most reliable encapsulation strategy is to dissolve both RNAs in the same aqueous buffer at the chosen mass (or charge) ratio and to use a single microfluidic mixing step at a moderate flow rate ratio (1:3 to 1:5 aqueous-to-ethanol). This approach keeps both RNAs in the same particle population with minimal surface exposure. Sequential addition — adding one RNA before the other — generally does not improve co-loading and often introduces reproducibility problems. Where high siRNA load is required, an ethanol-phase pre-solvation step for the siRNA may modestly improve loading by reducing the kinetic barrier to ion-pair formation with the ionizable lipid.

Table 3. mRNA + siRNA Co-Encapsulation Design Summary.

Co-Encapsulation of Gene-Editing mRNA and Guide RNA

Co-delivery of a gene-editor-encoding mRNA (such as Cas9 or base-editor mRNA) with a guide RNA is the central challenge of LNP-based in vivo gene editing. The two cargos must reach the same cell, escape the same endosome, and reach the nucleus at compatible times for the editor protein to engage its genomic target while the guide is still intact.

Key Considerations: Editor Expression, Guide RNA Stability, and Functional Timing

Gene-editing co-loading imposes several layered requirements:

• Editor mRNA drives protein output kinetics: The therapeutic window depends on a defined transient pulse of editor protein, which means the mRNA must produce sufficient protein within the limited window during which the guide is still intact.
• Guide RNA is the limiting reagent: Single-guide RNAs are short, susceptible to nuclease degradation, and prone to chemical modification drift; their per-particle copy number must be sufficient to engage every successfully translated editor protein.
• Functional timing is asymmetric: The editor mRNA takes hours to translate, while the guide must survive long enough to be present when the editor is active — placing the guide RNA in the same LNP as the mRNA is the most reliable way to ensure coordinated delivery.

LNP Design: Matching Component Ratios and Cytosolic Delivery Requirements

Editor mRNA is typically 1-4 kb (Cas9 mRNA) or 3-6 kb (base editor mRNA), while guide RNAs are 100-200 nt — a roughly 20- to 50-fold size difference. Charge-equivalent input ratios are usually preferred over mass-equivalent ones to avoid guide-RNA dominance of the ionizable lipid pool. PEG-lipid architecture is critical here: a C14 PEG-lipid at 1.5-2.0 mol% gives a useful compromise between storage stability and rapid exposure of the lipid surface after administration. Endosomal escape performance is best when the ionizable lipid pK_a sits in the 6.0-6.4 range, which is slightly more acidic than for pure mRNA applications and reflects the higher editor-mRNA load. Nanoparticle functionalization services can also introduce targeting ligands that bias delivery toward hepatocytes, hematopoietic stem cells, or other editing-relevant cell populations.

Encapsulation Strategies: Coordinated RNA Loading and Guide RNA Retention

Standard co-encapsulation uses the same single-step microfluidic mixing approach as for mRNA-plus-siRNA, with charge-balanced input ratios. Two additional practices improve guide RNA integrity: adding the guide RNA to the aqueous phase immediately before mixing (to minimize pre-mixing exposure to potential nucleases) and using a buffered aqueous phase with mildly acidic pH to keep the guide RNA in a stable conformational state. Guide RNAs that carry chemical modifications (2'-O-methyl, phosphorothioate end protection) generally co-encapsulate as efficiently as unmodified guides and substantially improve intracellular retention.

Table 4. Gene-Editing mRNA + Guide RNA Co-Encapsulation Design Summary.

Co-Encapsulation of Nucleic Acids and Small Molecules

Combining a nucleic acid with a small-molecule drug in the same LNP enables rational combination pharmacology in which both cargos are delivered with matched pharmacokinetics and predictable stoichiometry. The challenge is that the two cargos operate through fundamentally different encapsulation mechanisms: the nucleic acid binds ionizable lipid electrostatically, while the small molecule partitions into the lipid bilayer according to its lipophilicity.

Key Considerations: Solubility, Lipid Affinity, and Release Timing

Successful small-molecule-plus-nucleic-acid co-loading depends on resolving three paired challenges:

• Solubility mismatch between phases: Nucleic acids are aqueous-phase soluble, while lipophilic small molecules prefer the ethanol phase; hydrophilic small molecules prefer the aqueous phase. Both populations must end up in the same particle, which means the partition behavior of the small molecule must be deliberately directed.
• Lipid affinity shapes retention: Highly lipophilic molecules intercalate into the bilayer and release slowly; hydrophilic molecules escape rapidly. The release profile of each cargo can be tuned by adjusting its chemical structure or by adding ion-pair or metal-complex counterions.
• Functional timing may need to be sequential: A small-molecule inhibitor may need to act before the nucleic-acid-encoded protein reaches functional levels; conversely, a nucleic-acid-induced target may need to be expressed before the small molecule engages it. The release kinetics of each cargo should be matched to the desired biological sequence.

LNP Design: Accommodating Nucleic Acid Binding and Small-Molecule Partitioning

For lipid nanoparticles used in small-molecule delivery, the standard LNP four-component lipid system (ionizable lipid, helper lipid, cholesterol, PEG-lipid) is generally preserved, but the lipid ratios are adjusted to accommodate the additional cargo. Cholesterol content is typically raised modestly to expand the bilayer capacity for lipophilic small molecules, and the helper lipid is sometimes switched to DOPE for more fluid bilayers that load hydrophilic small molecules more readily. The ionizable lipid pK_a is selected primarily by the nucleic acid requirement; the small molecule is matched to the resulting pH environment rather than driving it.

Encapsulation Strategies: Selecting Loading Phases and Simultaneous or Sequential Loading

Two practical loading strategies are commonly used. In the simultaneous approach, the small molecule is dissolved in either the ethanol phase (for lipophilic compounds) or the aqueous phase (for hydrophilic compounds) before single-step mixing, which produces a particle with both cargos in similar proportions. In the sequential approach, the nucleic acid is encapsulated first by standard mixing, then the small molecule is loaded by pH-gradient-driven or ion-gradient-driven uptake into the pre-formed particle — useful when the small molecule would otherwise interfere with nucleic-acid ion pairing during the first mix. The choice depends primarily on the partition coefficient and aqueous solubility of the small molecule, and on whether the small molecule is tolerated in the same phase as the nucleic acid.

Table 5. Nucleic Acid + Small Molecule Co-Encapsulation Design Summary.

Co-Encapsulation of Protein or Peptide Antigens and Adjuvants

Co-encapsulating a protein or peptide antigen with an immunological adjuvant (TLR agonist, saponin, or STING activator) within the same LNP is the foundation of self-adjuvanted subunit vaccines. The biological rationale is that productive immune priming requires the same antigen-presenting cell to receive both the antigen and the maturation signal; delivering them in the same particle dramatically improves the probability that this condition is satisfied.

Key Considerations: Antigen Integrity and Adjuvant Compatibility

Antigen-adjuvant co-loading is governed by two practical concerns:

• Antigen structural integrity is non-negotiable: Conformational epitopes drive most neutralizing antibody responses, so the encapsulation process must avoid organic-solvent exposure, extreme pH, and excessive sonication that could denature the antigen.
• Adjuvant compatibility must be checked individually: Some adjuvants (saponins, certain TLR agonists) are surface-active and may disrupt bilayer integrity at high loading, while others are well tolerated at the same load. Each combination requires an explicit compatibility check.
• Antigen-adjuvant ratio affects immune outcome: Excess adjuvant relative to antigen can produce off-target immune responses and can mask the intended antigen signal; excess antigen with insufficient adjuvant fails to mature the presenting DC population.

LNP Design: Matching Lipid Composition to Antigen and Adjuvant Properties

For lipid nanoparticles used in antigen delivery, the LNP formulation typically shifts toward milder conditions than those used for nucleic acid delivery. Ethanol content during mixing is reduced, mixing times are shortened, and the temperature is held at 4-25°C to preserve protein structure. Helper-lipid choice is biased toward DOPC or DOPE for more fluid bilayers that accommodate larger protein cargoes, and the ionizable lipid content is sometimes reduced relative to the standard nucleic-acid formulation to limit surface exposure of the protein. The adjuvant is selected and dosed to provide the maturation signal at a level matching the antigen copy number per particle.

Encapsulation Strategies: Selecting Mild Loading Conditions and Limiting Payload Loss

Mild encapsulation methods are essential. Lipid-film hydration followed by extrusion can be used for larger proteins that tolerate the process, while microfluidic mixing at low ethanol fraction works for smaller proteins and peptides. Where the antigen is highly sensitive, pre-formation of empty LNPs followed by pH- or ion-gradient-driven antigen uptake preserves protein structure better than direct mixing. Adjuvants are typically loaded simultaneously with the antigen in the same phase — most small-molecule TLR agonists are aqueous-phase soluble and can be added to the aqueous buffer — while hydrophobic saponin adjuvants partition into the lipid phase and are added to the ethanol phase before mixing.

Table 6. Antigen + Adjuvant Co-Encapsulation Design Summary.

Co-Encapsulation of Gene-Editing RNPs and Donor DNA

Co-delivery of a CRISPR ribonucleoprotein (RNP — Cas9 or Cas12 protein pre-assembled with guide RNA) with a donor DNA template for homology-directed repair (HDR) is the most demanding combination in this resource: it spans three distinct cargo chemistries (protein, nucleic acid, DNA) and requires coordinated delivery to the same nucleus at compatible concentrations.

Key Considerations: RNP Activity, Donor DNA Properties, and Intracellular Timing

RNP-plus-donor-DNA co-encapsulation must satisfy three constraints simultaneously:

• RNP activity must be preserved through encapsulation: The pre-assembled RNP is a large protein-RNA complex that can denature or dissociate under harsh encapsulation conditions. The process must keep the RNP intact from encapsulation through intracellular delivery.
• Donor DNA must be protected yet bioavailable: Donor templates are typically 500-2000 bp single- or double-stranded DNA; they must be protected from extracellular nuclease degradation but must ultimately access the nucleus during HDR, ideally while the RNP is generating the double-strand break.
• Functional timing of editor and donor must overlap: HDR is most efficient when the donor template is present at the moment the RNP generates the break. Co-encapsulation that releases both cargos into the same nuclear microenvironment at the same time is therefore the design goal.

LNP Design: Protecting RNP Structure and Accommodating Donor DNA

For lipid nanoparticles used in CRISPR RNP delivery, the formulation typically uses a more neutral ionizable lipid pK_a (around 6.0) to minimize exposure of the RNP to acidic conditions during endosomal transit. Helper-lipid selection favors DOPE for its hexagonal-phase promotion that supports efficient endosomal escape of large complexes. Donor DNA is treated as a long anionic nucleic acid for charge-equivalent input calculation, similar to long mRNA, and the total nucleic acid mass is held below the level that would destabilize the RNP. PEG-lipid content (1-2 mol%) is chosen to preserve colloidal stability without sterically blocking the RNP surface.

Encapsulation Strategies: RNP Preassembly and Controlled Co-Loading with Donor DNA

The most reliable strategy is to pre-assemble the RNP at the optimal protein-to-guide-RNA ratio and verify its activity before encapsulation, then introduce the RNP and the donor DNA into the aqueous phase of a microfluidic mixing process. The aqueous pH is held at mildly acidic values (6.5-7.0) to keep the RNP in its active conformation, and the ethanol phase fraction is limited to maintain RNP integrity. Sequential loading — adding donor DNA first, then driving RNP uptake by pH gradient — can be used when the donor DNA is small enough to load efficiently and the RNP is too fragile for direct co-mixing.

Table 7. RNP + Donor DNA Co-Encapsulation Design Summary.

Common Co-Encapsulation Problems and How to Address Them

Even when each individual cargo is well understood, combining them in a single LNP introduces failure modes that rarely appear in single-payload formulations. The four problems below are the most common; each one can be diagnosed with the indicators listed and addressed with the solutions proposed.

One Payload Loads Efficiently While the Other Remains Free

Cause: The two payloads do not share the same encapsulation driver. The most common version is a nucleic acid that binds the ionizable lipid efficiently paired with a small-molecule, protein, or peptide that has no affinity for the lipid phase and remains in the external buffer. Charge mismatch, size mismatch, or solubility mismatch are typical root causes.

Indicator: Bulk fluorescence-based nucleic acid quantification or HPLC analysis shows high total encapsulation efficiency for one cargo and near-zero for the other; particle size and PDI remain consistent with the well-encapsulated payload only.

Proposed Solution: Troubleshooting services for LNP encapsulation typically begin by screening the encapsulation phase of the under-loaded species (ethanol versus aqueous), adjusting its input amount, or chemically pre-modifying it to introduce a positive charge (for anionic cargos) or a hydrophobic anchor (for small hydrophilic cargos). For proteins, switching from co-mixing to post-formation gradient-driven uptake often resolves the asymmetry.

High Bulk Encapsulation Masks Low Single-Particle Co-Loading

Cause: The bulk encapsulation efficiency is high because most particles contain at least one copy of each cargo — but the particle population is heterogeneous: some particles contain payload A only, others payload B only, and only a minority contain both. This is the single most misleading diagnostic in co-encapsulation work.

Indicator: Bulk assay reports EE% > 80% for each cargo individually; single-particle analysis (fluorescence co-localization, mass cytometry, or cryo-EM tomography) shows that fewer than 30% of particles contain both payloads.

Proposed Solution: Move from bulk mixing to a method that forces both payloads into the same particle, such as pre-forming a cargo-cargo complex before mixing (for example, ion-pairing a small molecule with a nucleic acid) or sequential loading where the second payload is driven into already-loaded LNPs by a gradient. Verify with single-particle fluorescence co-localization before drawing biological conclusions.

Payload Ratios Drift During Purification or Storage

Cause: The two cargos have different retention characteristics during TFF, dialysis, or buffer exchange, or different stability profiles in the final storage buffer. The ratio that worked at encapsulation is not the ratio at the time of administration.

Indicator: The measured payload ratio shifts between the post-encapsulation time point and the post-TFF or post-storage time point; one payload leaks more rapidly than the other during stability studies.

Proposed Solution: Audit each downstream step with per-payload quantification: TFF molecular-weight cutoff, buffer composition, storage temperature, and cryoprotectant choice can each preferentially retain or release one payload. Adjusting the cryoprotectant and storage buffer to equalize stability across payloads is often the most efficient fix. For lyophilized formats, screen cryoprotectants that stabilize both cargos simultaneously.

Both Payloads Reach Cells but the Combined Function Remains Weak

Cause: Cellular uptake is intact and the particles contain both cargos, but the intracellular release or functional engagement of one payload is poor. This is the most subtle failure mode because every bulk and uptake assay looks fine.

Indicator: Fluorescence or radiolabel co-localization confirms both cargos inside target cells; functional readout (protein expression, gene editing, knockdown) shows one or both cargos performing below expected levels.

Proposed Solution: Use functional reporters for each payload independently to localize the bottleneck — is the issue that one cargo is degraded in the endosome, that release kinetics are mismatched, or that the two cargos are competing for shared intracellular machinery? Adjusting ionizable lipid pK_a, helper lipid composition, or the order in which the cargos are released can re-balance the functional output.

Recommended LNP Co-Encapsulation Services at BOC Sciences

BOC Sciences provides integrated scientific support across the full co-encapsulation workflow — from initial payload compatibility assessment through process development, payload-specific characterization, and functional co-delivery evaluation. The three service tracks below map directly to the technical decisions described in the preceding sections.

Payload Compatibility Assessment and LNP Formulation Design

Every co-encapsulation project begins with an assessment of payload compatibility — solubility, charge behavior, stability, and the encapsulation phase each payload naturally prefers. Method development for LNP encapsulation at BOC Sciences combines this assessment with formulation design across the full four-component lipid system: ionizable lipid screening, helper-lipid selection, cholesterol optimization, and PEG-lipid architecture. The deliverable is a defined lead formulation with predicted performance characteristics before the first scale-up batch is produced.

Co-Encapsulation Process Development and Payload Ratio Optimization

Once the formulation is defined, microfluidic LNP production services deliver reproducible co-encapsulation at scales from milligrams to grams, with per-payload input ratio control and consistent particle size and PDI. Process development covers single-step simultaneous loading, sequential gradient-driven loading, and hybrid approaches where one cargo is loaded by direct mixing and the other by post-formation uptake. The team also tunes flow rate ratio, total flow rate, and post-mixing dilution to optimize encapsulation efficiency for both cargos simultaneously.

Payload-Specific Characterization and Functional Co-Delivery Evaluation

Lipid nanoparticle characterization for co-encapsulation goes beyond the standard single-payload panel. Per-payload encapsulation efficiency is quantified by species-specific Ribogreen, HPLC, or ELISA methods. Single-particle co-localization is assessed by fluorescence microscopy or mass cytometry. Stability is monitored by per-payload integrity assays across the storage interval, and functional co-delivery is evaluated in cell-based assays that report the activity of each cargo independently and in combination. This integrated characterization workflow distinguishes genuine co-loading from bulk-level masking and is the foundation of confident process decisions.

Table 8. BOC Sciences Services for Multi-Payload LNP Co-Encapsulation.