Biomimetically enhanced demineralized bone matrix for bone regenerative applications

Demineralized bone matrix (DBM) is one of the most widely used bone graft materials in dentistry. However, the ability of DBM to reliably and predictably induce bone regeneration has always been a cause for concern. The quality of DBM varies greatly depending on several donor dependent factors and also manufacturing techniques. In order to standardize the quality and to enable reliable and predictable bone regeneration, we have generated a biomimetically-enhanced version of DBM (BE-DBM) using clinical grade commercial DBM as a control. We have generated the BE-DBM by incorporating a cell-derived pro-osteogenic extracellular matrix (ECM) within clinical grade DBM. In the present study, we have characterized the BE-DBM and evaluated its ability to induce osteogenic differentiation of human marrow derived stromal cells (HMSCs) with respect to clinical grade commercial DBM. Our results indicate that the BE-DBM contains significantly more pro-osteogenic factors than DBM and enhances HMSC differentiation and mineralized matrix formation in vitro and in vivo. Based on our results, we envision that the BE-DBM has the potential to replace DBM as the bone graft material of choice.


INTRODUCTION
Bone is the second most transplanted organ in the human body (Marino and Ziran, 2010). Bone grafting is used in several aspects of medicine ranging from placement of dental implants and spinal fusions to regenerating lost bone resulting from trauma or congenital anomalies. With respect to children, over 75% of birth defects are craniofacial anomalies (such as cleft palate) that require bone reconstruction procedures (Zuk, 2008). Finally, with the many wars around the globe, the incidence of injuries requiring bone reconstruction is at an all time high.
Over the past decade several natural and synthetic biomaterials have been developed to aid bone regeneration (George and Ravindran, 2010). However, they have not been able to replace currently used bone graft materials successfully. On the other hand, the focus of current research has shifted away from improving the performance of existing clinical materials. The most immediate clinical need lies in the generation of products that improve the performance of existing materials or modified versions of existing clinical materials with improved performance. The focus of this study is the generation of a modified bone graft material with superior osteoinductive properties.
The gold standard for bone regenerative procedures is autografts. In situations that require significant quantity of bone to be regenerated, donor site morbidity becomes an issue with autografts. Under these circumstances, bone graft materials such as allograft bone are used. DBM is a commonly used allograft bone material. It is most commonly used in appendicular, axial and craniofacial bone regenerative applications (Gruskin et al., 2012). However, The quality and effectiveness of commercial DBM varies with processing techniques and several donor dependent factors (Zhang et al., 1997;Schwartz et al., 1998;Lohmann et al., 2001;Traianedes et al., 2004). As a result, bone regeneration and augmentation procedures do not have predictable outcomes. Additionally, the osteoinductive and osteogenic capacity of allograft DBM is significantly lesser than autografts (Marino and Ziran, 2010).
Very few medical products have as much variability in composition and performance as commercially available clinical grade DBM. Several inconsistencies have been reported with respect to DBM: The presence of osteoinductive growth factors (such as BMPs) varies significantly between batches of DBM and even amongst samples from the same batch (Bae et al., 2006(Bae et al., , 2010. DBM from female donors has been shown to contain higher quantities of BMPs (Pietrzak et al., 2006). DBM shows variability in performance depending on donor age (Schwartz et al., 1998) and finally revascularization of DBM and allograft bone is poor (Delloye et al., 2007). Recently, several approaches have been studied to enhance the effectiveness of DBM such as remineralization (Soicher et al., 2013;Horváthy et al., 2015)and use of platelet rich plasma (Han et al., 2009) with limited and varied results. DBM in combination with bone marrow aspirates has been used to treat bone cysts effectively (Park et al., 2008;Di Bella et al., 2010), but it is not as effective when used for fracture healing and large quantity bone regenerative applications (Drosos et al., 2015).
Clinically, in order to augment bone regeneration, recombinant BMP2 is used clinically. Although it is very potent, dosage issues and ectopic effects are major problems facing BMP2 usage. Many complications have been reported recently causing serious safety concerns among clinicians (Thibault et al., 2010;Zara et al., 2011).
We have attempted to solve the inherent problems associated with DBM by generating a biomimetically-modified version of clinical grade DBM. We have achieved this by incorporating the native extracellular matrix (ECM) of differentiating mesenchymal stem cells (MSCs) within it. We chose MSCs as the source cell for creating the ECM, as the resulting matrix would be a combination of MSC matrix and that of MSCs differentiating into osteoblasts. This can provide an ideal environment for patient specific MSCs. The other alternative would be osteoblasts. However, osteoblasts have limited proliferative ability and hence would not be able to populate the DBM as effectively as MSCs. We have published previously on the standardization of conditions and advantages of using biomimetic scaffolds for tissue regeneration (Ravindran et al., 2012(Ravindran et al., , 2014b. We have used these techniques to develop a modified clinical product with enhanced performance. The aim of this study was to evaluate the ability of our biomimetically enhanced DBM (BE-DBM) in comparison with commercial DBM using in vitro and in vivo experimental models to analyze if the BE-DBM depicts improved stem cell attachment, proliferation and differentiation abilities.

Cell Culture
Human marrow stromal cells were used in this study (HMSCs). These primary cells were obtained from NIH-funded center for research resources, Tulane Center for the preparation and distribution of adult stem cells. The cells are representative of marrow stromal cells from five donors between the age groups of 19 and 29 consisting of both male and female donors (Sekiya et al., 2002). We have published previously using these cells and they have been verified for multipotetncy (Ravindran et al., 2012(Ravindran et al., , 2014a(Ravindran et al., , 2015. The cells were cultured in αMEM basal media (Gibco) with 20% FBS (Gibco), 1% L-glutamine (Gibco) and 1% antibiotic-antimycotic solution (Gibco).

Generation of BE-DBM
BE-DBM was generated using clinical grade commercial DBM. Two different types of DBM were used to generate BE-DBM. For the in vitro experiments, we used DBM granules alone. For the in vivo experiments, we used DBM granules containing cortical bone chips to serve as internal control for mineralized matrix. For each of the two types of DBM, we used three vials to generate the BE-DBM. Once the BE-DBM was prepared, they were stored as lyophilized samples until required for experimental use.
BMSCs were seeded on to the DBM at a concentration of 1 million cells per 250 mg of DBM granules and cultured in standard BMSC culture media for a period of 24 h. After this, the cells were cultured for 2 weeks in osteogenic culture media (growth media containing100 µg/ml ascorbic acid, 10 mM β-glycerophosphate and 10 mM dexamethasone). This was performed to induce osteogenic differentiation of the BMSCs and to facilitate the generation of a pro-osteogenic matrix. After 2 weeks, the DBM granules containing BMSCs were decellularized using our published protocol (Ravindran et al., 2012(Ravindran et al., , 2014a. Briefly, the samples were incubated for 1 h at 37 • C in TBS containing 0.5% triton x-100. After this, the cells were lysed using 25 mM ammonium hydroxide solution. They were then washed extensively in TBS followed by one wash in HBSS. Finally, DNAse digestion was performed and the samples were washed in double deionized water extensively, lyophilized and stored. Decellularization was verified by immunostaining for tubulin and DAPI nuclear staining.

Proliferation Experiment
Twenty thousand HMSCs were seeded on to equal amounts of DBM and BE-DBM in quadruplicates. Eight hours post seeding, the unattached cells were removed by aspiration and the samples were washed using three exchanges of fresh media to ensure complete removal of all unattached cells. Twenty-four hours post seeding, the number of live cells was quantitatively measured using an MTT cell titer assay (Promega). The number of cells present at various time points up to 1 week was also measured to obtain the proliferation rate.

Electron Microscopy
Electron microscopic evaluation was performed on DBM and BE-DBM in their natural state as well as when subjected to in vitro mineralization. To generate mineralized DBM and BE-DBM, in vitro mineralization experiment was performed as per previously published protocols (Ravindran et al., 2014b). Electron microscopic evaluation of the samples was performed after coating the samples with platinum and palladium using Hitachi S3000 electron microscope. Energy dispersive X-ray (EDX) analysis in variable pressure mode was performed to obtain elemental information on the mineralized samples and also to obtain ratios of calcium to phosphorus in the samples. For all EDX analyses, the samples were not coated.
In Vitro Differentiation of HMSCs 500,000 HMSCs were seeded on to 50 mg of DBM or BE-DBM and cultured in standard growth media for 2 weeks in quadruplicates. After 2 weeks, the RNA was isolated from both sets of samples. After first strand synthesis (BioRad first strand synthesis kit), quantitative real time PCR (qPCR) was performed using gene specific primers. Table 1 lists the primer sequences used in this study. All expression data were normalized to housekeeping genes GAPDH and B2M.

In Vivo Implantation
All experiments were performed in accordance with approved animal care protocols (Assurance No: A3460-01). 500,000 HMSCs were seeded on to 50 mg of DBM or BE-DBM encapsulated in collagen sponges (Zimmer collagen tape) and implanted subcutaneously on the back of 2-month-old athymic male nude mice for a period of 2 weeks. Experiments were performed in triplicate. We had two groups one with commercial DBM and the other with BE-DBM. Two implants were placed on the back of each mouse. On one side, we placed the DBM implant and the other side contained the BE-DBM implant. Therefore, a total of three mice were used for this study. After 2 weeks, the samples were extracted, fixed in 4% neutral buffered formalin, paraffin embedded and sectioned.
Fluorescent microscopy was performed using a Zeiss LSM 710 laser scanning confocal microscope or a BioRad Zoe fluorescent microscope. For all comparative samples, the imaging parameters were maintained constant. For peroxidase stained sections, microscopy was performed using a Zeiss Axio Observer D1 microscope or an EVOS XL Core microscope (Life Technologies).

Quantitation of Proteins in DBM and BE-DBM
ELISA was used to quantitate the amount of a few important proosteogenic proteins in the DBM and BE-DBM. Equal amounts of both materials (10 mg) were placed in 96 well plates in quadruplicates. The material was blocked with 5% BSA for 1 h and incubated with the appropriate primary antibody overnight at 4 • C. The samples were then washed four times in PBS and incubated with a biotinylated secondary antibody (1/250, Vector Laboratories) and then subsequently washed four times with PBS and incubated with peroxidase conjugated avidin (Vector Laboratories) for 1 h at room temperature. Finally, the samples were incubated with an ELISA substrate (Turbo TMB ELISA substrate, Thermo Scientific) for 5 min at room temperature. The reaction was stopped by the addition of 1 M sulfuric acid. The solution was then transferred to empty 96 well plate wells and absorbance at 490 nm was recorded. The following primary

Gene
Forward Reverse

Statistical Analysis
Student's t-test was performed for the indicated experiments to verify statistical significance. A P < 0.05 (95% confidence interval) was considered as statistically significant.

Characterization of BE-DBM for Enhanced Presence of Pro-osteogenic Proteins
DBM and BE-DBM sections were immunostained for the presence of several ECM proteins and growth factors that play an important role in osteogenesis and osteogenic differentiation of MSCs. Figure 1 shows representative images of 3D confocal microscopy. Results presented in Figure 1 show that the BE-DBM contains more pro-osteogenic proteins when compared to the commercially available DBM. The BE-DBM was generated using the DBM from the same container and hence, the results are directly comparable. In the results presented in Figure 1, tubulin was used as a negative control to show the absence of intracellular proteins (Figures 1B,B1). DAPI staining was performed to show the absence of cellular DNA (Figures 1C,C1). Rabbit and mouse secondary antibody controls were performed to show absence of non-specific staining (Figures 1D,D1).
ELISA was used to quantify the increased presence of fibronectin, BMP2, VEGF, and phosphorylated proteins. The graph presented in Figure 1K shows a statistically significant increase in the presence of these proteins within the BE-DBM when compared to DBM.

Electron Microscopic Evaluation of DBM and BE-DBM
The microstructure of DBM and BE-DBM was evaluated using electron microscopy. Figure 2 represents results from  4). The quantified proteins were: Fibronectin (FIB), BMP2, VEGF, and phosphorylated proteins (P-ser/thr/tyr). Statistical significance was measured using student's t-test. *Represents statistical significance with P < 0.05 and # represents statistical significance with P < 0.1. Phosphorylated proteins were quantified using an antibody that recognizes phosphorylated serine, threonine and tyrosine residues.
Frontiers in Physiology | www.frontiersin.org  week. The data points represent mean of quadruplicates with standard deviation as error. The slope of the linear lines (dotted lines for DBM and solid lines for BE-DBM) provides the rate of proliferation. HMSCs in the BE-DBM showed a 34.52% increase in proliferation rate. The boxed region in the graph represents data obtained at day 1. A 34.07% (P < 0.01 by student's t-test) increase in initial cell attachment was seen in BE-DBM with respect to DBM. The data at all time points was statistically significant with P < 0.05. *above each point represents statistical significance. this experiment. Figures 2A,B are images of commercial DBM. Figures 2A1,B1 show the presence of HMSCs on the DBM before decellularization is performed. Figures 2A2,B2 show images of BE-DBM containing the cell-secreted ECM. Upon comparing Figures 2A,B pertaining to DBM with Figure 2A2 and Figure 2B2 pertaining to BE-DBM it is possible to observe increased presence of fibrillar structures within the BE-DBM samples. The white arrows in Figure 2A2 and Figure 2B2 point to these structures. These structures represent the ECM deposition within the DBM.

The BE-DBM Promotes Improved Stem Cell Attachment and Proliferation
An MTT assay was used to quantitate proliferation of HMSCs on DBM and BE-DBM. Results presented in Figure 3B show that the BE-DBM promotes improved stem cell attachment (boxed FIGURE 4 | In vitro regulation of osteogenic genes. The graph represents fold change in gene regulation of key pro-osteogenic genes and growth factors in BE-DBM with respect to control DBM. Data are represented as mean fold change obtained from quadruplicate experiments with standard deviation as error. Student's t-test used to obtain statistical significance with respect to control. *Represents significance of P < 0.05. area representing the 1 day time point). A 34.07% (P < 0.01 by student's t-test) increase in cellular attachment was observed in the BE-DBM compared to DBM. Rate of proliferation was obtained by calculating the slope of the lines representing proliferation of the cells over a period of 1 week. The results showed that the BE-DBM enhanced the rate of proliferation of HMSCs by 34.52%. Figure 3A shows representative images of HMSCs in DBM and BE-DBM after 1 day and 7 days. The images show qualitatively the increased presence of cells in the BE-DBM at these time points.

The BE-DBM Promotes Improved Osteogenic Differentiation of HMSCs in Vitro
HMSCs were cultured under normal growth conditions in both DBM and BE-DBM for 2 weeks. qPCR results presented in Figure 4 show a statistically significant change in the expression of several key pro-osteogenic proteins such as DMP1, phosphate regulating endopeptidase homolog X (PHEX) and osteocalcin. We also observed significant increase in the expression of osteogenic growth factors such as growth and differentiation factor 10 (GDF10) and FGF2 and pro angiogenic factor VEGF.

The BE-DBM Promotes Improved Matrix Mineralization in Vitro
The ability of DBM and BE-DBM to promote nucleation of calcium phosphate crystals was evaluated using an in vitro nucleation experiment. Under these conditions, the DBM did not nucleate a large amount of calcium phosphate crystals. Figures 5A,B show similar microstructure to DBM that was not subjected to in vitro nucleation experiment (Figures 2A,B). On the other hand, results presented in Figures 5A1,B1 show the presence several structures resembling nucleated calcium phosphate crystals. These images were obtained from pt/pd-coated samples of mineralized DBM and BE-DBM. In addition, imaging of mineralized DBM and BE-DBM was performed on uncoated samples in variable pressure mode. Results presented in Figure 5C show the presence of a few calcium phosphate crystals in the DBM samples. The bright areas in the image (white arrows) are calcium phosphate deposits. The presence of calcium and phosphorus was verified by EDX elemental analysis ( Figure 5D). The ratio of calcium to phosphorus in these deposits was 1.485 (S.D = 0.175, n = 8).

Results presented in
On the other hand, results presented in Figure 5C1 show a very robust deposition of calcium phosphate throughout the BE-DBM sample (white arrows). Presence of calcium and phosphorus was verified using EDX analysis ( Figure 5D1) and the ratio of calcium to phosphorus was 1.645 (S.D = 0.106, n = 8). The difference in the Calcium to phosphorus ratio between the two samples was statistically significant with a P-value of 0.033 using student's t-test.

The BE-DBM Promotes Improved Osteogenic Differentiation in Vivo
Gene expression data is not valuable if protein expression does not follow in vivo. HMSCs were seeded on to DBM and BE-DBM, wrapped in clinical grade collagen sponges and implanted subcutaneously for 2 weeks in immunocompromised mice. Results presented in Figure 6 show that the HMSCs in BE-DBM expressed higher amounts of osteocalcin, DMP1, BMP2, TGFβ1, and RUNX2 when compared to those in commercial DBM.

The BE-DBM Promotes Enhanced Mineralization and Vascularization in Vivo
The key to successful bone regeneration is collagen deposition and matrix mineralization. The 2-week explant sections were stained with H&E to observe general tissue architecture. Results presented in Figures 7A,A1 show more robust eosin staining in the BE-DBM sections compared to DBM sections indicating a higher presence of collagen. Alizarin red staining was performed to look for calcium deposition. Results presented in Figures 7B,B1 show that the BE-DBM containing sections showed more robust staining with alizarin red indicating a higher calcium deposition in the matrix.
The DBM that was used for generating the BE-DBM and control DBM samples for in vivo experiments contained cortical bone chips. The cortical bone chips served as an internal control for collagen presence and calcium presence in natural bone. The black arrows in Figures 7A,A1,B,B1 point to cortical bone chips.
Angiogenesis is vital for bone regeneration. Our results indicate that the BE-DBM contains more VEGF compared to commercially available DBM (Figures 1E,E1). We analyzed if this translated to improved vascularization in vivo. The BE-DBM sections showed a higher amount of von Willebrand factor positive endothelial cells than the DBM sections (Figures 7C,C1) indicating that the BE-DBM promoted migration of host endothelial cells better than DBM. We quantified the von Willebrand factor staining. Six images spanning three samples for each group were used for this purpose. In the BE-DBM samples, on an average 10.53% of the area in the images stained positive for von Willebrand factor as opposed to 2.15% in the DBM samples. Student's t-test on the data showed a P-value of 0.0196 indicating that the data was statistically significant.
Additionally, the DBM samples did not show any endothelial cells within the samples. In certain areas, we were able to observe endothelial cells in the periphery of the sample. However, these may include some mouse connective tissue as well. We included these areas as well in our calculation. The * in Figures 7C,C1 indicate cortical bone chips. When the H&E stained sections were imaged using a confocal microscope, RBCs were observed only in the BE-DBM sections indicating active blood flow (Figures 7D,D1). This data corroborates well with the von Willebrand factor staining of the samples that indicated that there were no endothelial cells within the DBM samples. The presence of RBCs were not scattered, but concentrated in the shape of vessels (yellow arrows in Figure 7D) indicating that they were not from random bleeding. Finally, no secondary antibody non-specific staining was observed in our experiments (Figures 7E,E1).

DISCUSSION
The ECM is a dynamic environment that dictates cellular behavior and tissue functionality. We have published several articles on the use of decellularized ECM as a biomimetic biomaterial for tissue regeneration (Ravindran et al., 2012(Ravindran et al., , 2014a. Decellularized biomimetic matrices have gained prominence recently and have been evaluated for several tissue engineering applications such as heart (Moroni and Mirabella, 2014), lung (Petersen et al., 2012;Calle et al., 2015), and cartilage (Schwarz et al., 2012). The advantage of these matrices over other biomaterials is that they can provide a tissue specific environment. Several studies have shown the effectiveness and safety of this process (Crapo et al., 2011). The limitation however, is the maintenance of tissue integrity (Moroni and Mirabella, 2014). In the case of DBM this is not an issue as the starting material itself is demineralized and decellularized bone particles.
In this study, we have characterized a biomimeticallyenhanced version of clinical DBM that has the potential to significantly improve the quality of bone regenerative procedures. Our results show that the BE-DBM contains significantly more pro-osteogenic factors. One of the significant observations was the increased presence of fibronectin.  Fibronectin binds several growth factors (Goerges and Nugent, 2004;Zhu and Clark, 2014). Therefore, an increase in fibronectin can result in increased sequestration of growth factors in vivo. Apart from fibronectin, growth factors such as VEGF, BMP2, and TGFβ1 were also observed in increased amounts in the BE-DBM compared to DBM. The BE-DBM also contained significantly higher amounts of phosphorylated proteins. Phosphorylated proteins serve as the source for inorganic phosphorus during hydroxyapatite nucleation. Therefore, the increased presence of these proteins was an encouraging sign that the BE-DBM may promote faster and better nucleation. Although the qualitative and quantitative data provided in this study is not an exhaustive list of proteins present in the matrix, they provide a good overview to summarize that the BE-DBM that we have generated contains significantly more pro-osteogenic proteins.
During bone regeneration, recruitment of MSCs to the site is critical for new bone formation. Therefore, a bone regenerative material should possess the ability to promote stem cell attachment and proliferation. The BE-DBM promoted improved stem cell attachment and proliferation compared to DBM indicating its enhanced potential to recruit stem cells. Additionally, the BE-DBM also promotes better osteogenic differentiation of MSCs compared to DBM.
Our results indicated statistically significant regulation of key pro-osteogenic genes. Our results indicated a significant increase in the expression levels of PHEX, DMP1 and OC. PHEX and DMP1 are extremely important for mineralized matrix formation and regulate FGF23 expression (Martin et al., 2011). PHEX is an endopeptidase that acts upon the mineralization inhibitor osteopontin to positively regulate mineralized matrix formation (Zhu and Clark, 2014). DMP1 is a multi-functional proosteogenic protein that possesses several intra and extracellular roles ranging from control of MSC differentiation to serving as a collagen binding protein that actively nucleates hydroxyapatite (He et al., 2003;He and George, 2004;Ravindran et al., 2008;Eapen et al., 2010). OC is one of the most abundant noncollagenous proteins in bone. OC acts as an endocrine hormone and plays a pivotal role in bone formation and increase in bone mineral density (Lee et al., 2007). Apart from these key regulators of bone formation, the BE-DBM also stimulated an increase in the expression levels of the pro-angiogenic growth factor VEGF and pro-osteogenic growth factors GDF10 (Kaihara et al., 2003;Marsell and Einhorn, 2009) and FGF2 (Hong et al., 2010;Kigami et al., 2013). These results indicated the enhanced potential of the BE-DBM to induce MSC differentiation.
When subjected to in vitro nucleation experiments to explore the calcium phosphate nucleating ability of the BE-DBM compared to DBM, the BE-DBM showed a more robust nucleating ability with calcium to phosphorus ratio similar to that of hydroxyapatite found in bone. Collectively, our in vitro experiments indicated that the BE-DBM is better than DBM in promoting stem cell attachment, proliferation, differentiation and hydroxyapatite nucleation.
When BE-DBM and DBM were compared in vivo in a subcutaneous implantation model with HMSCs, the BE-DBM promoted better collagen synthesis and formation of a better-calcified matrix as evidenced by our histological data. These observations are in line with our in vitro data that indicated the ability of the BE-DBM to promote these events better than DBM. Additionally, in line with the positive regulation of pro-angiogenic factors in vitro, the BE-DBM also promoted better migration of host endothelial cells and vascularization when compared to commercial DBM. Finally, fluorescence immunohistochemistry of the explant sections revealed that the BE-DBM was able to promote better osteogenic differentiation of MSCs by inducing higher levels of expression of pro-osteogenic non-collagenous proteins such as OC and DMP1, growth factors such as BMP2 and TGFβ1 (Yamamoto et al., 2000;Ozkan et al., 2007) and important pro-osteogenic transcription factors such as RUNX2 (Komori, 2008;Zhang et al., 2009). These results indicated that the BE-DBM accelerated osteogenic differentiation and matrix mineralization in vivo.
Overall, the data presented in this manuscript shows that the BE-DBM promotes better differentiation of HMSCs in vitro and in vivo. However, further investigation using large animal critical-size bone defect models is required to verify the improved osteoinductive properties of BE-DBM. Our efforts at present are focused on these models and if successful, this product can bring about standardization to the quality and performance of DBM that is critically lacking at present. DBM is widely used in craniofacial bone regeneration, spinal fusion and in non-union fracture healing in conjunction with autologous bone (Gruskin et al., 2012). Based on our results, we predict that the BE-DBM will enable faster regeneration of higher quality bone in these applications.
This is the first report that shows that it is possible to generate a biomimetic ECM incorporated DBM that has the potential replace the existing material. The amount of ECM incorporated within DBM to generate BE-DBM can be standardized by the use of cell lines and by controlling the cell number, density and culture conditions using a bioreactor. If these conditions are standardized, it is feasible to scale up the production of BE-DBM for commercial use.

ACKNOWLEDGMENTS
This work was supported by NIH grant DE023806, UIC Chancellor's Discovery fund award and UIC Proof of Concept award to SR.