key: cord-1050246-a96e3nwz
authors: Yu, Gary Z; Ramasamy, Thiruganesh; Fazzari, Marco; Chen, Xucai; Freeman, Bruce; Pacella, John J
title: Lipid nitroalkene nanoparticles for the focal treatment of ischemia reperfusion
date: 2022-01-01
journal: Nanotheranostics
DOI: 10.7150/ntno.62351
sha: d01e8f25cf06009baae0c51969a359155b91cacf
doc_id: 1050246
cord_uid: a96e3nwz

Rationale: The treatment of microvascular obstruction (MVO) using ultrasound-targeted LNP cavitation (UTC) therapy mechanically relieves the physical obstruction in the microcirculation but does not specifically target the associated inflammatory milieu. Electrophilic fatty acid nitroalkene derivatives (nitro-fatty acids), that display pleiotropic anti-inflammatory signaling and transcriptional regulatory actions, offer strong therapeutic potential but lack a means of rapid targeted delivery. The objective of this study was to develop nitro-fatty acid-containing lipid nanoparticles (LNP) that retain the mechanical efficacy of standard LNP and can rapidly target delivery of a tissue-protective payload that reduces inflammation and improves vascular function following ischemia-reperfusion. Methods: The stability and acoustic behavior of nitro-fatty acid LNP (NO(2)-FA-LNP) were characterized by HPLC-MS/MS and ultra-high-speed microscopy. The LNP were then used in a rat hindlimb model of ischemia-reperfusion injury with ultrasound-targeted cavitation. Results: Intravenous administration of NO(2)-FA-LNP followed by ultrasound-targeted LNP cavitation (UTC) in both healthy rat hindlimb and following ischemia-reperfusion injury showed enhanced NO(2)-FA tissue delivery and microvascular perfusion. In addition, vascular inflammatory mediator expression and lipid peroxidation were decreased in tissues following ischemia-reperfusion revealed NO(2)-FA-LNP protected against inflammatory injury. Conclusions: Vascular targeting of NO(2)-FA-LNP with UTC offers a rapid method of focal anti-inflammatory therapy at sites of ischemia-reperfusion injury.

Cardiovascular disease is a leading cause of death in the United States, with over 1 million Americans having a new or recurrent acute myocardial infarction (AMI) in 2020 [1] . Contemporary treatment for AMI is percutaneous coronary intervention (PCI), which aims to restore perfusion to the myocardium through recanalization of the epicardial vessels for maximal myocardial salvage [2] . Although mortality from AMI has decreased in recent years, post-MI congestive heart failure is increasing, due to subsequent microvascular obstruction (MVO) and inadequate restoration of microvascular perfusion, ultimately limiting myocardial salvage [3] .

MVO is a phenomenon in which myocardial tissue remains hypo-perfused after PCI, even in the face of patent upstream epicardial vessels. This is due to a combination of distal micro-embolization, ischemia-reperfusion injury, activation of inflammatory cascades and tissue edema that contribute to vessel compression and local vasospasm [4] [5] [6] [7] [8] [9] [10] . MVO occurs in up to 60% of all STEMI patients receiving PCI, thus decreasing LV function. MVO is an independent predictor for major adverse cardiac Ivyspring International Publisher events, which include cardiac death, stroke, myocardial infarction, and heart failure requiring hospitalization [11] [12] [13] . MVO is also associated with increased infarct size and LV remodeling, with persistence of MVO being a stronger predictor for functional recovery than transmural infarct extension [13] [14] [15] [16] [17] .

Previous strategies for limiting MVO include vasodilatory and antiplatelet drugs, thrombus aspiration, embolic protection devices and hyperoxic intracoronary reperfusion therapy [18] . No definitive therapeutic consensus for these various strategies for MVO has arisen, with the multiple clinical trials addressing these options yielding conflicting results [4, 6, 12] . Therefore, there is an unmet need for an acute therapy capable of resolving MVO and its inflammatory sequelae due to the unpredictable and rapidly catastrophic nature of acute cardiac events. In addition, the combination of inflammatory and oxidative stress induced vascular dysfunction includes not only cardiac contexts, but is relevant to other vascular pathologies including diabetes, peripheral vascular disease, and reperfusion injury to the vasculature of many organs [19] [20] [21] .

This unmet need is being addressed by the development and targeted delivery of anti-inflammatory electrophilic nitro-fatty acids (NO2-FA). These endogenous signaling mediators are generated by metabolic and inflammatory reactions of nitric oxide (NO) and nitrite (NO 2 -)-derived species with unsaturated fatty acids [22] . These small molecule electrophiles target specific reactive cysteines (Cys) present in the redox-sensitive proteome, undergoing a reversible and transient Michael addition-mediated protein post-translational modification (PTM). These selective PTM of hyperreactive Cys moieties in turn induce downstream adaptive signaling and gene expression responses [23] [24] [25] [26] . Diverse gene expression studies and murine models of cardiovascular injury affirm the pleiotropic engagement of anti-inflammatory signaling mechanisms by NO2-FA [27] [28] [29] [30] [31] [32] [33] [34] . The net effects are decreased production of reactive species, inhibition of pathogenic M1 to M2 macrophage phenotype activation, inhibition of fibrotic and hyperplastic processes and reversal of endothelial dysfunction [35] [36] [37] [38] [39] . All of these responses are relevant to the prevention and treatment of MVO, especially as systemically administered NO2-FA show cardioprotective effects in the setting of focal and global cardiac ischemic injury [29, [40] [41] [42] . In addition, NO 2 -OA inhibits xanthine oxidoreductase, a key pro-inflammatory source of reactive oxygen species in the vascular compartment [43, 44] . This protective effect has been demonstrated previously in a murine model of hypoxia-induced pulmonary hypertension as well [45] .

Notably, the targeted focal delivery of NO2-FA provides an immediate elevation in concentration of active drug at specific tissue sites, a novel and untested strategy for improving the pharmacokinetics of a covalent-modifier drug class [46] . Given the relatively rapid onset of signaling effects and a lack of adverse responses to 10-nitro-octadec-9-enoic acid administration in preclinical pharmacokinetics and toxicology studies and human Phase 1 and 2 trials, we envisioned that NO2-FA entrapped in lipid nanoparticles (LNP), their intravenous injection and subsequent targeted ultrasound (US)-induced intravascular release represents a viable potential therapy for MVO.

Therapeutic ultrasound-induced thrombolysis is a growing subject of investigation, with ultrasound-targeted cavitation (UTC) of drug-free LNP shown to improve tissue perfusion following MVO [47, 48] . This technique involves image-guided US-induced sonication of intravenously injected LNP contrast agents, resulting in LNP oscillation (cavitation) and the generation of intravascular shear forces. UTC produces both mechanical and biological effects by disrupting microthrombi, restoring perfusion, activating endothelial nitric oxide (NO) signaling and improving local vasodilation [48] [49] [50] . In addition to thrombolysis, UTC can be utilized for targeted delivery of therapeutics via drug-loaded LNP, resulting in site-specific concentration of the therapeutic agent, thus limiting off-target effects [51] [52] [53] [54] [55] . UTC is an ideal solution for treating MVO because it is a minimally invasive, theranostic technique that can visualize regions of MVO using LNP as US contrast agents, while simultaneously delivering image-guided ultrasound pulses.

We report herein a LNP formulation that contains a significant fraction of intercalated electrophilic NO2-FA (termed NO 2 -FA-LNP). These LNP were designed to a) augment the therapeutic efficacy of UTC for MVO, b) improve NO 2 -FA pharmacokinetics, c) facilitate the targeted delivery of NO 2 -FA, d) promote microvascular perfusion, e) induce anti-inflammatory responses and f) improve vascular protection. Herein, the physical properties, acoustic behavior and vascular effects in a rat hindlimb ischemia-reperfusion injury model reveal the therapeutic potential of NO2-FA-LNP. The rat hindlimb model mimics the microvascular structure of the heart and allows for US contrast-enhanced microvascular perfusion imaging in both a healthy state and upon ischemia-reperfusion injury. The results of this study indicated that NO2-FA-LNP treatment significantly limited oxidative and cytokine-associated inflammatory responses and improved hemodynamic parameters.

Nitro-fatty acid LNP were synthesized with a combination of 1,2-distearoyl-sn-glycero-3-phosphocholine, 1,2-Distearoyl-sn-Glycero-3-phosphoethanolamine-N -(methoxy(polyethylene glycol)-2000) (Avanti Polar Lipids Inc., Alabaster, AL), polyoxyethylene-40 stearate (Sigma Aldrich, St. Louis, MO), and 10-nitro-octadec-9-enoic acid (10-NO2-OA, NO 2 -FA). All components were combined in a glass vial with chloroform in a 29.1:5.2:43.8:21.9 mol ratio before the resulting solution was vaporized under an argon gas stream before vacuum storage. The dehydrated lipids were then rehydrated in acidic saline with a head of perfluorobutane gas (FluoroMed, LP, Round Rock, TX, USA) prior to sonication (XL2020, Qsonica LCC, Neton, CT). The resulting NO2-FA-LNP were then washed 3 times in acidic saline to remove unsonicated lipids from solution before being aliquoted into sealed glass vials containing perfluorobutane.

The NO 2 -FA-LNP were characterized for LNP concentration, size distribution, and loading efficiency of NO 2 -FA. All measurements were taken serially over 6 d post-synthesis to allow for tracking of stability in storage and NO 2 -FA content over time. Concentration and size distribution were measured using a Coulter Counter (Multisizer 3 Beckman Coulter, Fullerton, CA, USA). Structural characterization and quantitative analysis of 10-NO2-OA was performed by HPLC-ESI-MS/MS, using an analytical C18 Luna column (2 x 20 mm, 5 μm; Phenomenex) with a flow rate of 0.7 mL/min and a gradient solvent system of water 0.1% acetic acid (solvent A) and acetonitrile 0.1% acetic acid (solvent B). The gradient program was the following: 35-100% solvent B (0-3min) and 100% solvent B (3-4min) followed by 1 min re-equilibration to initial conditions. Detection of 10-NO2-OA was performed in negative mode using a QTRAP 6500+ triple quadrupole mass spectrometer (Sciex, Framingham, MA) with the following parameters: declustering potential -50 V, collision energy -42 eV, source temperature of 650°C, and a multiple reaction monitoring (MRM) transition 326.2/46. Quantification of 10-NO2-OA was performed by stable isotopic dilution analysis using a calibration curve using [ 15 After vortexing and centrifugation, the upper layer containing the NO 2 -FA was recovered, dried under nitrogen, and resuspended into 100 μl acetonitrile before HPLC-MS/MS analysis. The differential content of NO 2 -FA between the two sites was obtained by subtraction of respective NO 2 -FA concentrations.

High-speed microscopic imaging was used to visualize the dynamic behavior of the NO 2 -FA-LNP during ultrasound excitation using a microscopy system capable of recording up to 25 million frames-per-sec for 128 frames.

Animal studies were approved by the Institutional Animal Care and Use Committee at the University of Pittsburgh (protocol number 18042556). A rat hindlimb model permitted the study of both healthy microvasculature and microvasculature experiencing ischemia-reperfusion injury in the same rodent [56] . Anesthesia was induced using 2.5% inhaled isoflurane in 2-month-old male Sprague-Dawley rats (Charles Rivers, Pittsburgh, PA, USA) weighing 275 ± 20 g. The right femoral artery and right internal jugular vein were then cannulated for intravascular access. The distal right femoral artery was ligated, and the infusion line was advanced to the level of the iliac bifurcation for direct access to the left femoral artery. The jugular access was used to delivery DEFINITY ® for contrast-enhanced US imaging undiluted at a rate of 2 mL/hr. The left femoral access was used to deliver LNP +/therapeutic agents. Treatment groups for the experiments included NO 2 -FA alone with a vehicle of 85:15 polyethylene glycol to ethanol (Free NO 2 -FA), UTC using unmodified treatment LNP with co-infusion of free NO 2 -FA (Free NO 2 -FA+UTC), and UTC with NO 2 -FA-LNP infusion only (NO 2 -FA-LNP+ UTC).

For the UTC treatment, therapeutic US was administered using a single-element transducer operating at 1 MHz frequency (A303S, 0.5 inch, Olympus NDT, Waltham, MA), driven with an arbitrary function generator (AFG3252, Tektronix, Beaverton, OR) and a radio frequency power amplifier (800A3B, Amplifier Research, Souderton, PA). The ultrasound system was calibrated with a 200-µm capsule hydrophone (HGL-0200, Onda Corp, Sunnyvale, CA, USA). The treatment transducer was fixed vertically above the gastrocnemius region of the left rat hindlimb with the rat placed in right lateral decubitus position at a distance of approximately 1.5 cm from the hindlimb and was coupled to the hindlimb using acoustic gel.

The therapeutic US pulse (center frequency 1 MHz, peak negative acoustic pressure 1.5 MPa, pulse duration 5 ms) was delivered with 3 sec pulse interval to allow new LNP to reach the treatment area for 10 min for each treatment session. Each treatment session was followed by contrast-enhanced US imaging using a clinical imaging probe (Siemens, Sequoia, 15L8 probe) and infusion of DEFINITY ® . LNP were infused with automated syringe pumps and the syringes were rotated during administration to maintain LNP in suspension.

Contrast-enhanced US imaging was performed using the burst-replenishment technique in contrast pulse sequence mode at 7 MHz frequency with a mechanical index of 0.2 and a frame rate of 5 frames/sec. The imaging US transducer was positioned horizontally, parallel to the longitudinal axis of the rat tibia and perpendicular to the treatment transducer. The imaging transducer was manipulated such that the junction of the saphenous and popliteal arteries was visible in the field of view and the skin thickness was minimized. Occasional artifacts potentially representing bone reflections were permitted but ultimately excluded from any regions of interest for analysis. A 5-frame burst with mechanical index of 1.9 was used to extinguish contrast LNP from the field of view. Both the initial burst and subsequent reperfusion of the hindlimb with contrast LNP were recorded for further processing and analysis of hemodynamic parameters. All other US parameters including dynamic range (60 dB), gain (0 dB), and compression curve (linear) were kept constant throughout the studies for all treatment groups.

Processing of all recorded cine-loops from burst-replenishment imaging was performed using in-house code in MATLAB as previously [56] . Microvasculature regions of interest were selected for the gastrocnemius microvasculature such that skin, bone, and major vessels (saphenous and popliteal) were excluded. Image brightness (representing 60 dB range) of the region of interest was analyzed as a function of time for each cine-loop (approx. 30 sec) and fit to an exponential regression ( ) = �1 − − � , where is the plateau value is the inverse time constant. The product * is the initial slope of the curve (accounting for the steepness of the increase of the brightness to the plateau value over time). Hemodynamically, the plateau value was taken to represent the microvascular blood volume while the product * was taken to represent the microvascular blood flow rate.

Treatment groups for the healthy hindlimb model were centered on the analysis of tissue delivery of the loaded NO 2 -FA and included free NO 2 -FA alone, UTC of NO 2 -FA with co-infusion of unmodified LNP, and UTC of NO 2 -FA-LNP. The dosage of NO 2 -FA in all treatment groups was constant and represented the amount of NO 2 -FA content of 1×10 9 NO 2 -FA-LNP. Similarly, all LNP dosing (regardless of NO 2 -FA loading) were 1×10 9 LNP per treatment. All treatment infusions (NO 2 -FA or LNP infusions) were administered via the femoral cannulation at 3 mL/hr. All imaging LNP infusions were administered via the internal jugular cannulation at 2 mL/hr. Placement of the therapeutic transducer over the gastrocnemius muscle was confirmed by visual inspection and one pulse of LNP destruction in the field of view prior to treatment. After each 10-min treatment, infusion of imaging LNP was performed during burst-replenishment imaging and cine-loop recording. Rat physiologic parameters including heart rate, respiratory rate, and oxygen saturation were continuously monitored. After the sec 10-min treatment, the rat was euthanized by isoflurane overdose followed by heart excision. Following euthanasia, tissue samples were obtained from the UTC-treated gastrocnemius muscle tissue as guided by US imaging markers. Tissue samples were also collected from the ipsilateral quadriceps femoris muscle as a control for the UTC treatment receiving the same systemic perfusion of infused agents without targeted US stimulation. All tissue samples were then immediately frozen in liquid nitrogen and stored at -80°C.

Aside from the induction of ischemia-reperfusion injury, the protocol for the rat hindlimb model was identical to that of the healthy hindlimb model. Prior to treatment, the left femoral artery was ligated using a suture, resulting in isolated left hindlimb ischemia. After 1 hr ischemia, the suture was removed, followed by 30 min reperfusion of the hindlimb. Then, the treatment proceeded as with the healthy hindlimb model. After the sec 10 min treatment and perfusion imaging, there was a 2 hr interval to allow for development of pathophysiologic changes in gene expression before animal euthanasia and tissue sample collection.

Malondialdehyde (MDA), measured as a thiobarbituric acid reactive substance (TBARS), is a product of enzymatic and non-enzymatic unsaturated fatty acid oxidation. Skeletal muscle tissue samples were homogenized in ice-cold buffer and centrifuged at 12,000 g for 15 min at 4°C. After centrifugation, supernatants were processed for TBAR products at 532 nm. TBA reacts with MDA to form a TBA product detectable at 532 nm (ε = 1.56 × 10 5 M −1 cm −1 ). Results are expressed per milligram of tissue protein measured using a standard Bradford assay (Thermo Fisher Scientific, Waltham, MA, USA).

The skeletal muscle tissue samples from the treatment and control groups previously described were homogenized in the presence of TRIzol reagent (ThermoFischer Scientific, Waltham, MA, USA) using an Ultrasonic Processor (Heat Systems, XL-2020). Chloroform (200 µL) was added to 1 mL of TRIzol solution, centrifuged at 12,000 g for 15 min at 4°C, and 200 µL of aqueous upper layer was pipetted into an RNAse-free centrifuge tube. After subsequent treatment with isopropyl alcohol and 75% ethanol, the RNA pellet was dissolved in DEPC water. Complementary DNA was prepared from 2 μg of total RNA using TaqMan reverse transcription kit (Applied Biosystems, Foster City, CA, USA). RT-PCR amplifications were performed with the SYBR™ Green PCR Master Mix (Thermo Scientific, Waltham, MA, USA) using an CFX96 Connect™ Real-Time PCR Detection System (Bio-Rad, USA). Target genes included intercellular adhesion molecule 1 (ICAM-1), vascular cell adhesion molecule 1 (VCAM-1), monocyte chemotactic protein 1 (MCP-1), tumor necrosis factor alpha (TNF-α), interleukin-6 (IL-6), and nuclear factor kappa-light-chain-enhancer of activated B cells (NF-κB). The relative mRNA levels of target genes were normalized to GAPDH mRNA. The primer sequence used for RT-PCR analysis includes: 

All statistical analyses were performed in Prism (GraphPad Prism version 8.00, GraphPad Software, La Jolla, California, USA). Analyses were performed as either one-way ANOVA or two-way repeated measures ANOVA when appropriate. Post-hoc analyses for two-way repeated measures ANOVA were performed using Sidak's multiple comparisons test, while post-hoc for one-way ANOVA used Tukey's multiple comparisons test. Significance was taken at p<0.05. Error bars indicate standard deviation (SD).

The size and size distribution of NO 2 -FA-LNP were measured by Coulter counter analysis (Fig. 1) for up to 4 d post-synthesis. There were no significant differences in NO 2 -FA-LNP diameter (3.0 ± 1.5 µm) over 4 d of storage, with mean NO 2 -FA-LNP concentration dropping ~15% from d 1 onward. Size distribution curves depict a unimodal population similar to that of previous LNP measurements [57] . The NO 2 -FA content of NO 2 -FA-LNP was serially measured up to 4 d post-preparation (Fig. 2) . The average concentration was 82.9 ± 5.8 nmol NO 2 -FA per 1×10 9 LNP after subtraction of the subnatant containing NO 2 -FA that were not LNP-associated. Because the therapeutic dose for LNP previously established in the rat hindlimb model is 1×10 9 LNP/mL delivered at 3 mL/hr, the NO 2 -FA content present in 1×10 9 LNP (given a total treatment time of 20 min) was also used as the dosage present in free NO 2 -FA and free NO 2 -FA+UTC groups [58] .

High-speed microscopy during US stimulation of NO 2 -FA-LNP revealed that NO 2 -FA-LNP behaved similarly as control LNP. Consecutive still frame images of a high-speed movie are shown in Fig. 3 (1 MHz, 1.5 MPa). Since a negative peak acoustic pressure of 1.5 MPa is well above the inertial cavitation threshold, these images demonstrate typical US-induced morphological changes, including destruction of the LNP, loss of spherical conformation and daughter LNP formation.

Perfusion changes in contrast-enhanced ultrasound imaging Burst-replenishment imaging representative still-frame images taken at 5 sec post-burst after each 10 min treatment for two UTC-treated healthy hindlimb groups are shown in Fig. 4 . As the NO 2 -FA-LNP group featured direct incorporation of NO 2 -FA into the LNP structure, comparison of these images versus co-infusion with unmodified LNP illustrates the additional effects of NO 2 -FA incorporation over its presence in the vascular compartment.

The NO 2 -FA-LNP group induced a greater area coverage with greater image intensity of contrast-visualized microvascular reperfusion as compared to control conditions. Free NO 2 -FA+UTC does not impact image intensity and reperfusion as compared to baseline at 5 sec post-burst. Although this is not representative of a persistent hypoperfused region given that at 30 sec post-burst, the hypointense region was successfully reperfused, this abridged comparison emphasizes the improved rate of microvascular reperfusion induced by NO2-FA-LNP treatment. Still-frame visualization demonstrated increased speed of microvascular perfusion of the NO 2 -FA-LNP group that was further reinforced by quantification of microvascular perfusion using region-of-interest selection.

Hindlimb cine-loops were quantified using an exponential regression for region-of-interest image intensity ( Fig. 5 and 6 ). Although both NO2-FA-LNP and free NO 2 -FA+UTC groups increased microvascular blood volume, only the NO 2 -FA-LNP group demonstrated increased microvascular flow rate. The administration of free NO 2 -FA did not affect hindlimb microvascular perfusion, revealing that while UTC significantly increased blood volume, the incorporation of NO 2 -FA into LNP was required for enhancement of microvascular perfusion. 

Burst-replenishment still-frame images from contrast-enhanced US imaging of healthy hindlimb model -Still-frame observational analysis at 5 sec post-burst shows drastic differences in replenishment between NO2-FA-LNP+UTC and Free NO2-FA+UTC groups. Much of the microvascular bed is yet to be replenished in the latter, suggesting possible microvascular slowing or previously discussed microvascular spasm, while the former group shows full replenishment of the microvasculature exceeding baseline levels. TX1 for treatment 1, TX2 for treatment 2 imaging periods after a 10-min treatment. 

Tissue concentrations of NO 2 -FA at both US treated and untreated sites for the three groups are shown (Fig. 7) . The administration of free NO 2 -FA showed no difference in tissue concentration when no UTC was applied to the hindlimb. NO 2 -FA co-infusion with UTC and NO 2 -FA-LNP +UTC showed sequentially increasing NO 2 -FA concentration. The prior incorporation of NO 2 -FA into the LNP gave ~2x increase in tissue delivery of NO 2 -FA as compared to NO 2 -FA co-infused with control LNP.

Perfusion changes measured by contrast-enhanced ultrasound imaging

Still frames from burst-replenishment cine-loops are shown for the NO 2 -FA-LNP and NO 2 -FA co-infusion with standard UTC groups (Fig. 8) . The NO 2 -FA-LNP group showed significant increases in perfusion compared to the post-IR state while the NO 2 -FA co-infusion group showed no improvement in perfusion. Quantitative analysis of hindlimb perfusion showed NO 2 -FA-LNP treatment significantly increased in microvascular blood volume and microvascular blood flow ( Fig. 9 and 10 ).

RT-PCR analysis of pro-inflammatory chemokine expression showed UTC-induced NO 2 -FA administration decreased tissue ICAM-1, VCAM-1, MCP-1, and TNF-α mRNA expression (Fig. 11) . Lipid oxidation byproduct measurements of TBA-reactive species per mg protein for the three groups revealed that NO 2 -FA-LNP +UTC treatment decreased the generation of TBARS, compared to both free NO 2 -FA and free NO 2 -FA+UTC groups (Fig. 12 ). 

This study reveals that an NO 2 -FA-containing lipid LNP can be locally targeted via image-guided therapeutic US for NO 2 -FA release in the vascular compartment of a rodent hindlimb. These multi-lamellar lipid membranes consisted of di-stearoyl phosphatidylcholine, di-stearoyl phosphatidylethanolamine linked to PEG-2000, polyoxyethylene-40 stearate and having a 22% mol ratio of 10-nitro-octadec-9-enoic acid, the active pharmacological agent. This formulation gave a focal tissue delivery of NO2-FA that significantly increased microvascular blood flow and suppressed inflammatory cytokine transcription and oxidative stress following tissue ischemia-reperfusion injury. This affirms that NO 2 -FA can be functionalized in a LNP vehicle to focally deliver a chemically reactive, anti-inflammatory agent when LNP are disrupted by ultra-sound induced cavitation (Fig. 13) . This nanotechnology-based drug delivery strategy is novel, since previous preclinical and clinical studies of NO2-FA therapeutics have utilized intraperitoneal, sub-cutaneous, intravenous or oral systemic administration routes. Thus, the present approach, can limit off target effects and better treat acutely developing, localized pathologies via the rapid concentration of a therapeutic NO2-FA to primary sites of need. 

The fatty acid nitroalkene derivative used herein is a synthetic homolog of endogenously generated mediators that are present in nM concentrations in plants, fish and mammals [22, 59] . Unsaturated fatty acids are nitrated by diverse metabolic and inflammatory reactions of NO and nitrite (NO2 -)-derived reactive species that ultimately give rise to the nitrogen dioxide radical ( . NO 2 ). The addition of an electron-withdrawing nitro (R-NO 2 ) substituent on a fatty acid double bond confers an electrophilic nature to the β-carbon of the double bond [60] . This electron-poor β-carbon is chemically reactive and will undergo a kinetically fast and reversible reaction with electron-rich biological nucleophiles such as the thiolate of cysteine (Cys). This reaction, termed Michael addition, will induce the structural and functional PTM of proteins that have functionally-significant, electrophile-reactive thiols adducted by NO 2 -FA [61] . In pure form NO 2 -FA can self-aggregate into micelles, displaying a critical micellar concentration in aqueous milieu of 5-50 µM [62] . The present study affirms that NO 2 -FA stably reside in multilamellar phospholipid membranes as the free acid, where structural integrity and electrophilic chemical reactivity is preserved for days. This unique LNP formulation thus both capitalizes and expands upon on the 25+ yr clinical use of artificial lipid membranes (liposomes, LNP) in nanoscale drug delivery systems. Most recently, the LNP delivery of a mRNA construct has been highly effective for immunizing the population against the SARS-CoV-2 virus. Importantly, this clinical success further affirms the safety, utility and economic viability of using lipid nanoparticles to confer pharmacokinetic advantages to life-saving therapeutic agents via the tissue targeting of labile cargo.

When subjected to US-induced cavitation, ultra-high-speed microscopy of NO 2 -FA-LNP revealed acoustic behaviors similar to those of LNP in the absence of 22 mol% NO 2 -FA. This includes inertial cavitation characteristics and the formation of smaller daughter LNP, both viewed as significant to the therapeutic efficacy of lipid LNP in UTC therapy. These properties are also critical in the mechanical "chiseling" of microthrombi when relieving the physical obstruction associated with MVO [63] .

The mechanisms underlying the enhanced uptake of the LNP-associated NO2-FA cargo can include two physical properties of sonicated LNP, sonoporation and sonoprinting [64] . Sonoporation involves the formation of transient micropores in cellular membranes that are induced by LNP cavitational forces tangent to membrane surfaces. Increased endothelial barrier and membrane permeability at cellular junctions has also been reported [65] . While sonoporation is an attractive mechanism explaining NO2-FA-LNP delivery, the absence of enhanced NO 2 -FA uptake in the free NO 2 -FA+UTC group (utilizing control LNP) argues against sonoporation-promoted tissue uptake.

Sonoprinting involves deposition of LNP components onto cellular membranes as a result of radial oscillatory forces [66] . Via this mechanism, the NO2-FA cargo can be rapidly trafficked to intracellular targets by associating with the CD36 scavenger receptors on macrophages, the family of fatty acid binding proteins found in all cells and, upon NO 2 -FA-membrane and membrane-membrane contact, via diffusional processes [67, 68] [69] . Sonoprinting may thus explain the increased NO 2 -FA uptake for the NO 2 -FA-LNP+UTC group, as opposed to the free NO 2 -FA+UTC group, as incorporation of NO 2 -FA into LNP lamellae was the distinguishing factor between the two. Given that NO 2 -FA must associate with and traverse membranes by diffusional or endocytic mechanisms for gaining access to intracellular compartments such as the cytosol, binding proteins, nuclei and mitochondria, sonoprinting likely facilitates these functions [31] .

To date, preclinical and clinical studies of NO2-FA therapeutics have utilized systemic delivery strategies. It is shown herein that UTC can rapidly and focally enhance tissue delivery of NO 2 -FA, with two sequential 10 min UTC treatments significantly increasing local skeletal muscle NO 2 -FA concentration well over that of adjacent untreated sites. While the chronic systemic administration of NO 2 -FA has not shown significant safety signals at therapeutic concentrations in humans, the rapid focal delivery of NO 2 -FA remains desirable for instigating protective and adaptive signaling responses in acute and more localized pathologies.

The electrophilic character of NO 2 -FA induces reversible Michael addition with Cys thiolates present in proteins and other small molecules occurs. The reaction of NO 2 -FA with specific hyperreactive protein thiols can directly inhibit pro-inflammatory enzymes that have functionally significant Cys moieties. Examples of enzymatic targets in this category include xanthine oxidoreductase, NADPH oxidases, cyclooxygenase and 5-lipoxygenase [70] . NO2-FA also exert anti-inflammatory responses by modifying transcription factor and signal transduction pathway activities. For example, NO 2 -FA activate the anti-inflammatory transcriptional regulatory proteins Kelch-like ECH-associated protein 1/ nuclear factor (erythroid-derived 2)-like 2 (Keap1/Nrf2) and peroxisome proliferator-activated receptor gamma (PPARγ) [22, 34, 71] . NO2-FA also inhibit pro-inflammatory signaling responses regulated by Toll-like receptors (TLR), nuclear factor kappa-light-chain-enhancer of activated B cells (NF-κB), janus kinase/signal transducer and activator of transcription proteins (JAK/STAT) and stimulator of interferon genes (STING) [30, [72] [73] [74] . Via these pleiotropic actions, NO2-FA promote an antioxidant and adaptive signaling milieu that limit pathogenic inflammatory cell function, vaso-occlusion and downstream vessel wall remodeling.

These effects were in part evidenced by an inhibition of tissue lipid oxidation by NO2-FA-LNP +UTC treatment but not by free NO 2 -FA alone or free NO 2 -FA+UTC. There was also a significant reduction in the expression of numerous inflammatory target genes that are expressed during ischemia-reperfusion injury and contribute to the sequelae of MVO. Specifically, ischemia-reperfusion injury promotes nuclear translocation of NF-κB and upregulates expression of TNF-α, a pro-inflammatory factor secreted by monocytes and vascular endothelial cells. This in turn induces the expression of pro-inflammatory cytokines including IL-6 and MCP-1, as well as adhesion molecules on the surface of vascular endothelial cells such as VCAM-1 and ICAM-1. This cascade is predictive of not only MVO but also future adverse cardiovascular events, as the resulting inflammation produces increased oxidative stress and tissue damage, ultimately worsening patient outcomes [75] . There were concurrent decreases in all of these inflammatory indices with NO2-FA-LNP+UTC treatment that were not seen in systemic administration of free NO 2 -FA alone or free NO 2 -FA+UTC.

Microvascular hemodynamic changes were assessed herein through contrast-enhanced US imaging. The enhanced local vessel and tissue targeting of NO 2 -FA induced by NO 2 -FA-LNP+UTC can increase NO bioavailability in tissues and the vascular compartment via multiple mechanisms. Notably, NO 2 -FA only show NO donor activities in vitro in aqueous phosphate buffer-based studies, an effect mediated via a modified Nef reaction. This NO 2 -FA decay reaction to NO appears to not be operative in more complex biological fluids and tissues where Michael addition is possible and a kinetically more facile reaction [76] . In support of this precept, preclinical pharmacokinetics studies and human Phase 1 and Phase 2 trials do not show an acute effect of intravenous or oral NO2-FA on blood pressure or pulse rate. This may not rule out other less direct NO and cGMP-dependent signaling mechanisms being enhanced by the local effects of NO 2 -FA-LNP+UTC. For example, NO 2 -FAs also increase eNOS mRNA and protein expression and eNOS serine-1177 phosphorylation. The net effect would be to increase the vascular endothelial caveolar translocation and enzymatic specific activity of eNOS [77] .

Given that previous studies of in vitro endothelial NO production after NO2-FA administration in vitro showed significant increases ~2 hr post-treatment, the gene expression responses and post-translational modifications of eNOS that can be induced by NO 2 -FA are less likely the etiology of the acute perfusion changes that were seen herein on the timescale of minutes. Future investigation can identify additional mechanisms responsible for the improved microvascular perfusion induced by NO2-FA-LNP+UTC, such as suppression of adhesion molecule expression and other processes of inflammatory cell-mediated vaso-occlusion [30] . Despite this unclear etiology, it is apparent that the combination of enhanced perfusion due to the anti-inflammatory and antioxidant effects of NO2-FA-LNP+UTC therapy may ameliorate MVO and ischemia-reperfusion injury seen after AMI.

Previous literature has shown that the inhibitions of various inflammatory signaling reactions by NO2-FA are both time-dependent and dosage-dependent in inflammatory and vascular cells [28] . The suppression of vascular inflammatory responses observed with NO 2 -FA-LNP+UTC treatment was consistent with those observed in the more chronic systemic administration of NO 2 -FA [29] . This, coupled with previous success in reducing inflammation and myocardial preservation in focal and global ischemia-reperfusion models by NO 2 -FA, suggests the strong potential of further improving therapeutic outcomes by rapidly concentrating NO 2 -FA at the site of the myocardial insult [29] . Moreover, hypertensive and oxidative stress-induced cardiac fibrosis and atrial fibrillation were also inhibited by NO 2 -FA administration, further affirming the pleiotropic anti-inflammatory and adaptive signaling actions induced by small molecule electrophiles [35, 38, 39] . The present results build upon this body of work by showing that targeted treatment can immediately induce significant changes in microvascular perfusion and gene expression responses can become evident as soon as 2 hr after NO2-FA-LNP+UTC treatment.

Limitations: There are limitations to this initial study that has motivated more comprehensive ongoing work. For NO 2 -FA-LNP+UTC therapy, additional observation intervals can be implemented to improve the measurement of short and long-term tissue loading kinetics and extend/expand the characterization of gene expression and hemodynamic parameter changes. Mechanistic analyses identifying the specific source of hemodynamic changes were also not performed; given previous role of NO pathways in UTC therapy, future investigations may include live in vivo detection of local changes in NO concentration.

Specific mechanics of LNP interactions with capillary endothelium were not explored in this study. However, our previous studies have shown that the microvascular architecture remains intact after this therapy. Future work may elucidate differences in LNP sizes in vitro (Fig. 3) versus in vivo in the vasculature through use of high-speed intra-vital microscopy. In addition, contrast-enhanced US is a well-validated technique for measurement of true microvascular perfusion, and the majority of microvascular perfusion is comprised of capillary blood flow. Moreover, improvement in myocardial perfusion, as assessed with contrast-enhanced US, is associated with better clinical outcomes. Analysis of multiple time intervals for NO2-FA delivery may also reveal key mechanisms of NO 2 -FA-LNP therapeutic efficacy and improve pharmacokinetic insight.

The sonolysis of NO 2 -FA-containing LNP revealed therapeutic potential for the acute treatment of vascular occlusion upon tissue ischemia-reperfusion. This rapid, targeted treatment suppressed inflammatory gene expression, limited oxidative stress and improved microvascular perfusion. This novel LNP technology improved the pharmacokinetics of chemically reactive electrophilic lipids when using focal ultrasound as a vehicle for targeted delivery. This therapeutic strategy can be especially suitable for treatment of localized sequelae of AMI, including MVO and ischemia-reperfusion injury, with its focus on concentrating drug payloads at the specific site of MVO. This also provides opportunities for synergy with the other aspects of UTC therapy, including enhanced microvascular perfusion and mechanical disruption of thrombi.

Sources of funding. GZY was supported by NIH T32

HL076124-13; R21-NS112787 (MAF); R21-HL152312 (JP); R01-HL058115, R01-HL64937, P30-DK072506, P01-HL103455 (BAF); This work was also supported by a material support grant for contrast agent from Lantheus Medical Imaging, Inc. North Billerica, Massachusetts.

Disclosures. BAF acknowledges an interest in Creegh Pharmaceuticals, the other authors have no conflicts of interest. 

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The authors have declared that no competing interest exists.