Name: modeling and simulations of olfactory drug delivery with passive and active controls of nasally inhaled pharmaceutical aerosols
Uploaded: 2016-05-20T14:00:00
Description: Watch this Scientific Journal Video about Modeling and Simulations of Olfactory Drug Delivery with Passive and Active Controls of Nasally Inhaled Pharmaceutical Aerosols at JoVE.com

This study was funded by Central Michigan University Innovative Research Grant P421071 and Early Career Grant P622911.

The MRI images were provided by the Hamner Institutes for Health Sciences and the usage of these images was approved by the Virginia Commonwealth University institutional review board.
1. Image-Based Nasal Airway Preparation
<ol>
	<li>Acquire magnetic resonance (MR) images of a healthy non-smoking 53-year-old male (weight 73 kg and height 173 cm) that consist of 72 coronal cross-sections spaced 1.5 mm apart spanning the nostrils to the nasopharynx4.</li>
	<li>Open Imaging ...

<ol>
	<li>Mistry, A., Stolnik, S., Illum, L. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Nanoparticles+for+direct+nose-to-brain+delivery+of+drugs.">Nanoparticles for direct nose-to-brain delivery of drugs.</a> Int. J. Pharm. 379 (1), 146-157 (2009).</li><li>Alam, S., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Development+and+evaluation+of+thymoquinone-encapsulated+chitosan+nanoparticles+for+nose-to-brain+targeting:+a+pharmacoscintigraphic+study.">Development and evaluation of thymoquinone-encapsulated chitosan nanoparticles for nose-to-brain targeting: a pharmacoscintigraphic study.</a> Int. J. Nanomedicine. 7 (11), 5705-5718 (2012).</li><li>Shi, H., Kleinstreuer, C., Zhang, Z. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Laminar+airflow+and+nanoparticle+or+vapor+deposition+in+a+human+nasal+cavity+model.">Laminar airflow and nanoparticle or vapor deposition in a human nasal cavity model.</a> J. Biomech. Eng. 128 (5), 697-706 (2006).</li><li>Si, X., Xi, J., Kim, J., Zhou, Y., Zhong, H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Modeling+of+release+position+and+ventilation+effects+on+olfactory+aerosol+drug+delivery.">Modeling of release position and ventilation effects on olfactory aerosol drug delivery.</a> Respir. Physiol. Neurobiol. 186 (1), 22-32 (2013).</li><li>Si, X., Xi, J., Kim, J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Effect+of+laryngopharyngeal+anatomy+on+expiratory+airflow+and+submicrometer+particle+deposition+in+human+extrathoracic+airways.">Effect of laryngopharyngeal anatomy on expiratory airflow and submicrometer particle deposition in human extrathoracic airways.</a> Open J. Fluid D. 3 (4), 286-301 (2013).</li><li>Xi, J., Longest, P. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Numerical+predictions+of+submicrometer+aerosol+deposition+in+the+nasal+cavity+using+a+novel+drift+flux+approach.">Numerical predictions of submicrometer aerosol deposition in the nasal cavity using a novel drift flux approach.</a> Int. J. Heat Mass Transfer. 51 (23), 5562-5577 (2008).</li><li>Illum, L. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Nasal+drug+delivery:+new+developments+and+strategies.">Nasal drug delivery: new developments and strategies.</a> Drug Discov. Today. 7 (23), 1184-1189 (2002).</li><li>El Taoum, K. K., Xi, J., Kim, J. W., Berlinski, A. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=In+vitro+evaluation+of+aerosols+delivered+via+the+nasal+route.">In vitro evaluation of aerosols delivered via the nasal route.</a> Respir. Care. 60 (7), 1015-1025 (2015).</li><li>Misra, A., Kher, G. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Drug+delivery+systems+from+nose+to+brain.">Drug delivery systems from nose to brain.</a> Curr. Pharm. Biotechnol. 13 (12), 2355-2379 (2012).</li><li>Hoekman, J. D., Ho, R. J. Y. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Effects+of+Localized+Hydrophilic+Mannitol+and+Hydrophobic+Nelfinavir+Administration+Targeted+to+Olfactory+Epithelium+on+Brain+Distribution.">Effects of Localized Hydrophilic Mannitol and Hydrophobic Nelfinavir Administration Targeted to Olfactory Epithelium on Brain Distribution.</a> Aaps Pharmscitech. 12 (2), 534-543 (2011).</li><li>Corley, R. A., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Comparative+Computational+Modeling+of+Airflows+and+Vapor+Dosimetry+in+the+Respiratory+Tracts+of+Rat,+Monkey,+and+Human.">Comparative Computational Modeling of Airflows and Vapor Dosimetry in the Respiratory Tracts of Rat, Monkey, and Human.</a> Toxicol. Sci. 128 (2), 500-516 (2012).</li><li>Shi, H., Kleinstreuer, C., Zhang, Z. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Modeling+of+inertial+particle+transport+and+deposition+in+human+nasal+cavities+with+wall+roughness.">Modeling of inertial particle transport and deposition in human nasal cavities with wall roughness.</a> J. Aerosol Sci. 38 (4), 398-419 (2007).</li><li>Kleinstreuer, C., Zhang, Z., Donohue, J. F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Targeted+drug-aerosol+delivery+in+human+respiratory+system.">Targeted drug-aerosol delivery in human respiratory system.</a> Annu. Rev. Biomed. Eng. 10 (4), 195-220 (2008).</li><li>Kleinstreuer, C., Zhang, Z., Li, Z., Roberts, W. L., Rojas, C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=A+new+methodology+for+targeting+drug-aerosols+in+the+human+respiratory+system.">A new methodology for targeting drug-aerosols in the human respiratory system.</a> Int. J. Heat Mass Transfer. 51 (23), 5578-5589 (2008).</li><li>Wilson, I. B. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=The+deposition+of+charged+particles+in+tubes,+with+reference+to+the+retention+of+therapeutic+aerosols+in+the+human+lung.">The deposition of charged particles in tubes, with reference to the retention of therapeutic aerosols in the human lung.</a> J. Colloid Sci. 2 (2), 271-276 (1947).</li><li>Wong, J., Chan, H. -. K., Kwok, P. C. L. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Electrostatics+in+pharmaceutical+aerosols+for+inhalation.">Electrostatics in pharmaceutical aerosols for inhalation.</a> Ther Deliv. 4 (8), 981-1002 (2013).</li><li>Bailey, A. G. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=The+inhalation+and+deposition+of+charged+particles+within+the+human+lung.">The inhalation and deposition of charged particles within the human lung.</a> Journal of Electrostatics. 42 (1), 25-32 (1997).</li><li>Xi, J., Si, X. A., Gaide, R. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Electrophoretic+particle+guidance+significantly+enhances+olfactory+drug+delivery:+a+feasibility+study.">Electrophoretic particle guidance significantly enhances olfactory drug delivery: a feasibility study.</a> PLoS ONE. 9 (1), e86593 (2014).</li><li>Martin, A., Finlay, W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Alignment+of+magnetite-loaded+high+aspect+ratio+aerosol+drug+particles+with+magnetic+fields.">Alignment of magnetite-loaded high aspect ratio aerosol drug particles with magnetic fields.</a> Aerosol Sci. Technol. 42 (4), 295-298 (2008).</li><li>Dames, P., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Targeted+delivery+of+magnetic+aerosol+droplets+to+the+lung.">Targeted delivery of magnetic aerosol droplets to the lung.</a> Nature Nanotechnology. 2 (8), 495-499 (2007).</li><li>Xi, J., Longest, P. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Transport+and+deposition+of+micro-aerosols+in+realistic+and+simplified+models+of+the+oral+airway.">Transport and deposition of micro-aerosols in realistic and simplified models of the oral airway.</a> Ann. Biomed. Eng. 35 (4), 560-581 (2007).</li><li>Longest, P. W., Xi, J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Effectiveness+of+direct+Lagrangian+tracking+models+for+simulating+nanoparticle+deposition+in+the+upper+airways.">Effectiveness of direct Lagrangian tracking models for simulating nanoparticle deposition in the upper airways.</a> Aerosol Sci. Technol. 41 (4), 380-397 (2007).</li><li>Xi, J., Zhang, Z., Si, X. A., Yang, J., Deng, W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Optimization+of+magnetophoretic-guided+drug+delivery+to+the+olfactory+region+in+a+human+nose+model.">Optimization of magnetophoretic-guided drug delivery to the olfactory region in a human nose model.</a> Biomech. Model. Mechanobiol. In. , (2015).</li><li>Longest, P. W., Hindle, M., Das Choudhuri, S., Xi, J. X. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Comparison+of+ambient+and+spray+aerosol+deposition+in+a+standard+induction+port+and+more+realistic+mouth-throat+geometry.">Comparison of ambient and spray aerosol deposition in a standard induction port and more realistic mouth-throat geometry.</a> J. Aerosol Sci. 39 (7), 572-591 (2008).</li><li>Xi, J., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Design+and+Testing+of+Electric-Guided+Delivery+of+Charged+Particles+to+the+Olfactory+Region:+Experimental+and+Numerical+Studies.">Design and Testing of Electric-Guided Delivery of Charged Particles to the Olfactory Region: Experimental and Numerical Studies.</a> Curr. Drug Deliv. 13 (9), 1-15 (2015).</li><li>Zhou, Y., Guo, M., Xi, J., Irshad, H., Cheng, Y. -. S. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Nasal+deposition+in+infants+and+children.">Nasal deposition in infants and children.</a> Journal of aerosol medicine and pulmonary drug delivery. 27 (2), 110-116 (2014).</li><li>Xi, J., Yuan, J. E., Si, X. A., Hasbany, J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Numerical+optimization+of+targeted+delivery+of+charged+nanoparticles+to+the+ostiomeatal+complex+for+treatment+of+rhinosinusitis.">Numerical optimization of targeted delivery of charged nanoparticles to the ostiomeatal complex for treatment of rhinosinusitis.</a> Int. J. Nanomedicine. 10 (7), 4847-4861 (2015).</li></ol>

A coupled image-CFD method was presented in this study that incorporated the image-based model development, quality meshing, airflow simulation, and magnetic particle tracking. Multiple software modules were implemented to this aim, which included functions of segmentation of medical images, reconstruction/meshing of anatomically accurate airway models, and flow-particle simulations. Using this numerical method, performances of three intranasal delivery protocols were tested and compared. Compared to in vitro ex...

Drugs delivered to the olfactory region can bypass the blood-brain-barrier and directly enter the brain, leading to an efficient uptake and quick action onset of the drugs1,2. However, conventional nasal devices such as nasal pumps and sprays deliver extremely low doses to the olfactory region (&#60; 1%) via the nasal route3,4. It is primarily due to the complicated structure of the human nose which is composed of narrow, convoluted passageways (Figure 1). The olfactory region locates above the superior meatus, where only a very small fraction of inhaled air can reach5,6. Furthermore, conventional inhalation devices depend on aerodynamic forces to transport therapeutic agents to the target area7. There is no further control over the motions of particles after their release. Therefore, the transport and deposition of these particles predominately depend on their initial speeds and release positions. Due to the convoluted nasal passage as well as the lack of particle control, the majority of drug particles are trapped in the anterior nose and cannot reach the olfactory region8.
While there are many choices of nasal devices, those designed specifically for targeted olfactory delivery have rarely been reported7,9. One exception is Hoekman and Ho10 who developed an olfactory-preferential delivery device and demonstrated higher cortex-to-blood drug levels in rats as opposed to using a nose drop. However, scaling the deposition results in rats to humans is not straightforward, considering the vast anatomical and physiological differences between these two species11. Many limitations exist when using adapted versions of standard nasal devices for olfactory deliveries. One primary setback is that only a very small portion of medications can be delivered to the olfactory mucosa, through which the medications may enter the brain. Numerical modeling predicted that less than 0.5% of intranasally administered nanoparticles can deposit in the olfactory region3,5. The deposition rate is even lower (0.007%) for micrometer particles12. In order to make the nose-to-brain delivery clinically feasible, the olfactory deposition rate has to be significantly improved.
There exist several possible approaches to improve the olfactory delivery. One approach is the smart inhaler idea proposed by Kleinstreuer et al.13 As particles depositing in one region are mainly from one specific area at the inlet, it is possible to deliver particles to the target site by releasing them only from certain areas at the inlet. The smart delivery technique has been shown to generate a much more efficient lung delivery than conventional methods.13,14 It is hypothesized that this smart delivery idea can also be applied in intranasal drug delivery to improve dosages to the olfactory mucosa. By releasing particles into different positions at the nostril opening and from different depths within the nasal cavity, improved olfactory delivery efficiencies and reduced drug waste in the anterior nose are possible.
Another possible method is to actively control the particle motion within the nasal cavity using a variety of field forces, such as electric or magnetic force. Electric control of charged particles has been suggested for targeted drug delivery to the human nose and lungs15-17. Xi et al.18 numerically tested the performance of electric guidance of charged particles and predicted significantly improved olfactory doses. Similarly, guidance of ferromagnetic drug particles with an appropriate magnetic field also has the potential to target particles to the olfactory mucosa. Behaviors of inhaled agents, if ferromagnetic, can be altered by imposing appropriate magnetic forces19. Dames et al.20 demonstrated that it is practical to target ferromagnetic particles to specific areas in mouse lungs. By packaging therapeutic agents with superparamagnetic iron oxide nanoparticles, the deposition in one lung of a mouse under the influence of a strong magnetic field was significantly increased compared to the other lung20.
Particles were assumed to be spherical and ranged from 150 nm to 30 &#181;m in diameter. The governing equation is21: 
(1)<img alt="Equation 1" src="/files/ftp_upload/53902/53902eq1.jpg" />
The above equation describes the motion of a particle governed by drag force, gravitational force, Saffman lift force 22, Brownian force for nanoparticles, and magnetophoretic force if placed in a magnetic field. Here, vi is the particle velocity, ui is the flow velocity, &#964;p is the particle response time, Cc is the Cunningham correction factor, and &#945; is the air/particle density ratio. To effectively guide the intranasally administered drugs to the olfactory region, it is necessary for the applied magnetophoretic forces to overcome both the particle inertia and gravitational force. In this study, a composite of 20% maghemite (&#947;-Fe2O3, 4.9 g/cm3) and 80% active agent was assumed, which give a density of approximate 1.78 g/cm3 and a relative permeability of 50. The selection of &#947;-Fe2O3 was due to its low cytotoxic. Iron (3+) ions are widely found in human body and a slightly higher ion concentration will not cause significant side-effects23.

<table border="0" cellpadding="0" cellspacing="0" width="659">
	<tbody>
		<tr height="21">
			<td height="21" style="height:21px;width:152px;">MIMICS 13</td>
			<td style="width:199px;">Materialise Inc, Ann Arbor, MI</td>
			<td style="width:188px;">MR image segmentation</td>
			<td style="width:120px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:152px;">Gambit</td>
			<td style="width:199px;">ANSYS Inc, Canonsburg, PA&#160;</td>
			<td style="width:188px;">Model development</td>
			<td style="width:120px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:152px;">ANSYS ICEMCFD</td>
			<td style="width:199px;">ANSYS Inc, Canonsburg, PA&#160;</td>
			<td style="width:188px;">Meshing</td>
			<td style="width:120px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:152px;">ANSYS Fluent</td>
			<td style="width:199px;">ANSYS Inc, Canonsburg, PA&#160;</td>
			<td style="width:188px;">Fluid and particle simulation</td>
			<td style="width:120px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:152px;">COMSOL Multiphsics</td>
			<td style="width:199px;">COMSOL Inc, Burlington, MA</td>
			<td style="width:188px;">Magnetic particle tracing</td>
			<td style="width:120px;"></td>
		</tr>
	</tbody>
</table>

modeling and simulations of olfactory drug delivery with passive and active controls of nasally inhaled pharmaceutical aerosols

There are many advantages of direct nose-to-brain drug delivery in the treatment of neurological disorders. However, its application is limited by the extremely low delivery efficiency (&#60; 1%) to the olfactory mucosa that directly connects the brain. It is crucial to develop novel techniques to deliver neurological medications more effectively to the olfactory region. The objective of this study is to develop a numerical platform to simulate and improve intranasal olfactory drug delivery. A coupled image-CFD method was presented that synthetized the image-based model development, quality meshing, fluid simulation, and magnetic particle tracking. With this method, performances of three intranasal delivery protocols were numerically assessed and compared. Influences of breathing maneuvers, magnet layout, magnetic field strength, drug release position, and particle size on the olfactory dosage were also numerically studied.
From the simulations, we found that clinically significant olfactory dosage (up to 45%) were feasible using the combination of magnet layout and selective drug release. A 64 -fold higher delivery of dosage was predicted in the case with magnetophoretic guidance compared to the case without it. However, precise guidance of nasally inhaled aerosols to the olfactory region remains challenging due to the unstable nature of magnetophoresis, as well as the high sensitivity of olfactory dosage to patient-, device-, and particle-related factors.

Control Case: 
Figure 3 displays the airflow field and particle deposition in the nasal airway with standard nasal devices. It clearly shows that airflow from the front nostril is ventilated to the upper passage and airflow from the back nostril is directed towards the nasal floor (Figure 3A). Aerosol particles are observed to move faster in the median passages and slower near the walls, forming an aerosol front in the mean flow dire...

Watch this Scientific Journal Video about Modeling and Simulations of Olfactory Drug Delivery with Passive and Active Controls of Nasally Inhaled Pharmaceutical Aerosols at JoVE.com

Modeling and Simulations of Olfactory Drug Delivery with Passive and Active Controls of Nasally Inhaled Pharmaceutical Aerosols

This manuscript reviews the modeling and simulations of different protocols to deliver medications to the olfactory region in image-based nasal airway models. Multiple software modules are used to develop the anatomically accurate nose model, generate computational mesh, simulate nasal airflows, and predict particle deposition at the olfactory region.

There are many advantages of direct nose-to-brain drug delivery in the treatment of neurological disorders. However, its application is limited by the ...

The overall goal of this methodology is to develop different protocols to deliver medications to the olfactory region in image based nasal airway models. This method can help answer key questions in attacking neurological drug delivery such as:Whether it is feasible to deliver adequate dosage to the olfactory region. How to control particle motions in the nose.What is the best practice for olfactory targeting? The main advantage of this technique is that a significantly enhanced olfactory dosage can be achieved. This is a critical step for nose to brain drug delivery.The implication of this technique extend towards therapy of brain tumors. Since drug particles deposited in the olfactory region can directly enter the brain. Begin by acquiring magnetic resonance, or MR images, of a healthy, nonsmoking 53 year old male, that consist of 72 coronal cross sections spaced 1.5 millimeters apart spanning the nostrils to the nasopharynx.Open the imaging software and import the MR images by clicking File, Import Images. Select the MR images and click OK.To construct the 3D model click Segmentation, then Threshold. To set the grayscale range between negative 1024 and negative 419.Click Segmentation and Calculate 3D. Next, click Segmentation and Calculate Polylines. Select the 3D body and click OK to generate the polylines that define the solid geometry.Export the polylines as an IGES file. Now, open the model development software, and click File, Import, and IGES to import the IGES file into the program. Then, click the Edge Command button on the right panel, click Create Edge, and select NURBS to reconstruct smooth contours.Click Face Command button, then, Form Face. Select Wire Frame to build a surface from edges. Continue to build all surfaces that cover the whole airway.Retain the nasal anatomical details such as the uvula, epiglottal fold, and laryngeal sinus. Click File, Export, IGES to export the nasal airway model. Next, open the meshing software.Click File, Import Geometry, Legacy, and STEPIES to import the nasal airway model. Click Create Parts to divide the airway surfaces into five different regions:The nasal vestibule, nasal valve, turbinate region, olfactory, and nasopharynx. Generate a computational mesh inside the airway by clicking Mesh, and Global Mesh Setup.Specify the maximum mesh size as 0.1 millimeters and click Apply. Finally, add a body fitted mesh in the near wall region by clicking Compute Mesh, Prism Mesh. Specify the number of layers as five, and the expanding ratio as 1.25 and click Apply.Begin by opening the model development software to develop the nasal model with front vestibular intubation. Click Volume, then Move Copy to change the location of the nebulizer catheter five millimeters into the vestibule from the nostril tip. Click Injection to release 150 nanometers of particles into the nostril.Then, open the fluid simulation software to compute particle deposition rates inside the nose. To compute the airflow field inside the airway, select the laminar flow model by clicking Define, Models, Viscous, and then choose Laminar under Viscous Model. To track particle motions select the Discrete Phase Model.Check Saffman Lift Force under Discrete Phase Model, click Report, and then choose Sample Trajectories. To find the number of particles deposited in the predefined olfactory region select Nasal under Boundaries and click Compute. Calculate the deposition rate as the ratio of the amount of deposited particles to the amount of particles entering the nostrils.Next, develop the nasal model with back vestibular intubation. Conduct the same procedure as done with the front. Click Volume, then Move Copy to change the location of the nebulizer catheter five millimeters into the vestibule from the rear nostril.Click Injection to release 150 nanometers of particles into the nostril. Proceed with deep intubation by inserting the nebulizer catheter right beneath the olfactory region. Release 150 nanometers of particles from the nebulizer.Use fluid and simulation software to compute particle deposition rates inside the nose on both total and local bases by following similar procedures as done for the vestibular intubation. Finally, repeat deep intubation while exercising breath holding and exhalation respectively. Click Define, then Boundary Conditions to open the Boundary Condition panel.Specify zero velocity at the two nostrils for breath holding. Specify vacuum pressure of 200 pascals at the nostrils, and zero pressure at the outlet for exhalation. Begin by opening magnetic particle tracking software.Click Geometry, and Rectangle to build the two plate channel. Click Rectangle to build the magnets around the two plate channel. Compute the particle trajectories and deposition rate by clicking Model 1, Laminar Flow, and Inlet 1.Then, specify the inlet velocity as 0.5 meters per second. Click Model 1, Magnetic Fields, and Magnetic Flux Conservation and specify the strength of the three magnets. Click Model 1, Particle Tracking for Fluid Flow, and Particle Properties.Specify the particle diameter and density, then click Inlet to release 3, 000 particles and to specify particle relative permeability, click Magnetophoretic Force and Compute. To find how many particles are depositing in the selected area, click Results, 1D Plot Group, and Plot. Calculate the deposition rate as the ratio of the amount of particles deposited in a certain area to the amount of particles entering the geometry.Next, to adjust the magnet's strength, click Model 1, then Magnetic Fields. Choose Magnetic Flux Conservation and change the magnet strength under Magnetization. Increase the magnet strength by an increment of one times ten to the fourth amps per meter and click Compute.Begin by applying the recently obtained magnetic strengths into a 2D nose model by putting three magnets one millimeter above the nose. Click Model 1, Geometry 1, to specify the size and position of the magnet. Then, click Model 1, Particle Tracking for Fluid Flow, and Inlet to release 3, 000 particles into the left nostril.Click Particle Properties to specify the particle size as 15 micrometers. Simulate the particle trajectories and subsequent olfactory delivery efficiencies by clicking Model 1, Laminar Flow, and Inlet 1. Specify the inlet velocity as 0.5 meters per second.Click Model 1, Magnetic Fields, and Magnetic Flux Conservation and specify the strength of the three magnets. Lastly, adjust the magnet layout and strength to improve olfactory delivery efficiency. To adjust the magnet's size and position click Model 1, then Geometry 1, then choose the magnet of interest and change the values of width, depth, height or X, Y and Z.Adjust magnet strength by clicking Model 1, then Magnetic Fields.Choose Magnetic Flux Conservation and change the magnet strength under Magnetization. Increase the magnet strength by an increment of one times ten to the fourth amps per meter, and click Compute. After completing testing in the 2D model, import the 3D nasal airway model into magnetic particle tracking software.Just as done for the 2D nose model, put four magnets one millimeter above the nose, and release 3, 000 particles of 15 micrometer diameter from one selected point. Use magnetic particle tracking software to track particle trajectories and compute olfactory delivery efficiencies by following similar procedures previously mentioned. Following the same procedure as before, adjust the magnet layout and strength in the 3D model to improve the target delivery to the olfactory region.Finally, test particle size ranging from one to 30 micrometers to find the right particle size for optimal magnetophoretic guidance to the olfactory region. Conventional nasal devices often deliver very low doses of drugs to the olfactory region due to the complicated structure of the nose. For vestibular intubation, there is a strong jedifact of particle release immediately downstream of the nasal.As expected, more drug particles are delivered to the olfactory region with front intubation than back, for both 150 nanometer and one micrometer particles. To assess performance of magnetophoretic guidance, a two plate channel was used to find the working magnet strength, followed by an idealized 2D nose model to find a baseline magnet layout, and then an image based 3D nose model to test the performance. The optimal olfactory dosage comes from aerosols in the range of 13 to 17 micrometers.Once mastered, this technique can be done well in two days, if conducted properly. While attempting this procedure, it's important to remember that procedures can be more time consuming for complex geometries. Following this procedure, other methods like electro guidance of charged particles can also be tested in order to answer whether charged particles can be used for effective olfactory drug delivery.After this development, this technique paved the way for researchers in the field of targeted drug delivery to explore the usage of magnetic field in the lungs or other organs. After watching this video, you should have a good understanding of how to improve drug delivery and conduct simulations with Fluent and Comsol.

modeling-simulations-olfactory-drug-delivery-with-passive-active

Research

JoVE Journal

Medicine

Osmotic Drug Delivery to Ischemic Hindlimbs and Perfusion of Vasculature with Microfil for Micro-Computed Tomography Imaging

Preclinical research in animal models of peripheral arterial disease plays a vital role in testing the efficacy of therapeutic agents designed to stimulate microcirculation. The choice of delivery method for these agents is important because the route of administration profoundly affects the bioactivity and efficacy of these agents1,2. In this article, we demonstrate how to locally administer a substance in ischemic hindlimbs by using a catheterized osmotic pump. This pump can deliver a fixed volume of aqueous solution continuously for an allotted period of time. We also present our mouse model of unilateral hindlimb ischemia induced by ligation of the common femoral artery proximal to the origin of profunda femoris and epigastrica arteries in the left hindlimb. Lastly, we describe the in vivo cannulation and ligation of the infrarenal abdominal aorta and perfusion of the hindlimb vasculature with Microfil, a silicone radiopaque casting agent. Microfil can perfuse and fill the entire vascular bed (arterial and venous), and because we have ligated the major vascular conduit for exit, the agent can be retained in the vasculature for future ex vivo imaging with the use of small specimen micro-CT3.

We show here the in vivo insertion of an osmotic pump for constant local drug delivery and the creation of hindlimb ischemia in a mouse model. Moreover, the hindlimb vasculature is perfused with Microfil, a silicone radiopaque agent, to prepare for micro-computed tomography (micro-CT) imaging.

Preclinical research in animal models of peripheral arterial disease plays a vital role in testing the efficacy of therapeutic agents designed to ...

Murine Model of Femoral Artery Wire Injury with Implantation of a Perivascular Drug Delivery Patch

Percutaneous interventions including balloon angioplasty and stenting have been used to restore blood flow in vessels with occlusive vascular disease. While these therapies lead to the rapid restoration of blood flow, these technologies remain limited by restenosis in the case of bare metal stents and angioplasty, or reduced healing and possibly enhanced risk of thrombosis in the case of drug eluting stents. A key pathophysiological mechanism in the formation of restenosis is intimal hyperplasia caused by the activation of vascular smooth muscle cells and inflammation due to arterial stretch and injury. Surgeries that induce arterial injury in genetically modified mice are useful for the mechanistic study of the vascular response to injury but are often technically challenging to perform in mouse models due to the their small size and lack of appropriate sized devices. We describe two approaches for a surgical technique that induces endothelial denudation and arterial stretch in the femoral artery of mice to produce robust neointimal hyperplasia. The first approach creates an arteriotomy in the muscular branch of the femoral artery to obtain vascular access. Following wire injury this arterial branch is ligated to close the arteriotomy. A second approach creates an arteriotomy in the main femoral artery that is later closed through localized cautery. This method allows for vascular access through a larger vessel and, consequently, provides a less technically demanding procedure that can be used in smaller mice. Following either method of arterial injury, a degradable drug delivery patch can be placed over or around the injured artery to deliver therapeutic agents.

We describe a surgical technique that produces wire injury in the femoral artery of mice to induce neointimal hyperplasia to serve as a model testing system for the perivascular delivery of therapeutic compounds for the inhibition of restenosis.

Percutaneous interventions including balloon angioplasty and stenting have been used to restore blood flow in vessels with occlusive vascular disease. ...

Intraluminal Drug Delivery to the Mouse Arteriovenous Fistula Endothelium

Delivery of therapeutic agents to enhance arteriovenous fistula (AVF) maturation can be administered either via intraluminal or external routes. The simple murine AVF model was combined with intraluminal administration of drug solution to the venous endothelium at the same time as fistula creation. Technical aspects of this model are discussed. Under general anesthesia, an abdominal incision is made and the aorta and inferior vena cava (IVC) are exposed. The infra-renal aorta and IVC are dissected for clamping. After proximal and distal clamping, the puncture site is exposed and a 25 G needle is used to puncture both walls of the aorta and into the IVC. Immediately after the puncture, a reporter gene-expressing viral vector was infused in the IVC via the same needle, followed by 15 min of incubation. The intraluminal administration method enabled more robust viral gene delivery to the venous endothelium compared to administration by the external route. This novel method of delivery will facilitate studies that explore the role of the endothelium in AVF maturation and enable intraluminal drug delivery at the time of surgical operation.

After puncturing the aorta through the inferior vena cava (IVC) to create an aorto-caval fistula in the mouse, solution containing a drug is infused into the IVC via the same needle, followed by incubation. This method enables more robust drug delivery to the venous endothelium compared to the external route.

Delivery of therapeutic agents to enhance arteriovenous fistula (AVF) maturation can be administered either via intraluminal or external routes. The ...

Pancreatic Duct Infusion: An Effective and Selective Method of Drug and Viral Delivery

The pancreas is a bifunctional organ with both endocrine and exocrine components. A number of pathologies can afflict the pancreas, including diabetes, pancreatitis, and pancreatic cancer. All three of these diseases mark active areas of study, not only to develop immediate therapy, but also to better understand their pathophysiology. There are few tools to further these areas of study. Pancreatic duct infusion is an important technique that can allow for lineage tracing, gene introduction, and cell line-specific targeting. The technique requires the intricate dissection of the second portion of the duodenum and ampulla, followed by the occlusion of the bile duct and the cannulation of the pancreatic duct. Although the technique is technically challenging at first, the applications are myriad. Ambiguity in the specifics of the procedure between groups highlighted the need for a standard protocol. This work describes the expression of a green fluorescent protein (GFP) within the pancreas after the pancreatic duct infusion of a viral vector expressing GFP versus a sham surgery. The infusion and therefore expression is specific to the pancreas, without expression present in any other tissue type.

Pancreatic duct infusion is an important technique that can allow for lineage tracing, gene introduction, and cell line-specific targeting. A pancreatic duct infusion technique for drug and viral delivery to pancreatic cells is presented here.

The pancreas is a bifunctional organ with both endocrine and exocrine components. A number of pathologies can afflict the pancreas, including diabetes, ...

Optimized LC-MS/MS Method for the High-throughput Analysis of Clinical Samples of Ivacaftor, Its Major Metabolites, and Lumacaftor in Biological Fluids of Cystic Fibrosis Patients

Defects in the cystic fibrosis trans-membrane conductance regulator (CFTR) are the cause of cystic fibrosis (CF), a disease with life-threatening pulmonary manifestations. Ivacaftor (IVA) and ivacaftor-lumacaftor (LUMA) combination are two new breakthrough CF drugs that directly modulate the activity and trafficking of the defective CFTR-protein. However, there is still a dearth of understanding on pharmacokinetic/pharmacodynamic parameters and the pharmacology of ivacaftor and lumacaftor. The HPLC-MS technique for the simultaneous analysis of the concentrations of ivacaftor, hydroxymethyl-ivacaftor, ivacaftor-carboxylate, and lumacaftor in biological fluids in patients receiving standard ivacaftor or ivacaftor-lumacaftor combination therapy has previously been developed by our group and partially validated to FDA standards. However, to allow the high-throughput analysis of a larger number of patient samples, our group has optimized the reported method through the use of a smaller pore size reverse-phase chromatography column (2.6 &#181;m, C8 100 &#197;; 50 x 2.1 mm) and a gradient solvent system (0-1 min: 40% B; 1-2 min: 40-70% B; 2-2.7 min: held at 70% B; 2.7-2.8 min: 70-90% B; 2.8-4.0 min: 90% B washing; 4.0-4.1 min: 90-40% B; 4.1-6.0 min: held at 40% B) instead of an isocratic elution. The goal of this study was to reduce the HPLC-MS analysis time per sample dramatically from ~15 min to only 6 min per sample, which is essential for the analysis of a large amount of patient samples. This expedient method will be of considerable utility for studies into the exposure-response relationships of these breakthrough CF drugs.

Ivacaftor and ivacaftor-lumacaftor combination are two new CF drugs. However, there is still a dearth of understanding on their PK/PD and pharmacology. We present an optimized HPLC-MS technique for the simultaneous analysis of ivacaftor and its major metabolites, and lumacaftor.

Defects in the cystic fibrosis trans-membrane conductance regulator (CFTR) are the cause of cystic fibrosis (CF), a disease with life-threatening ...

Improved Method for the Establishment of an In Vitro Blood-Brain Barrier Model Based on Porcine Brain Endothelial Cells

The aim of this protocol presents an optimized procedure for the purification and cultivation of pBECs and to establish in vitro blood-brain barrier (BBB) models based on pBECs in mono-culture (MC), MC with astrocyte-conditioned medium (ACM), and non-contact co-culture (NCC) with astrocytes of porcine or rat origin. pBECs were isolated and cultured from fragments of capillaries from the brain cortices of domestic pigs 5-6 months old. These fragments were purified by careful removal of meninges, isolation and homogenization of grey matter, filtration, enzymatic digestion, and centrifugation. To further eliminate contaminating cells, the capillary fragments were cultured with puromycin-containing medium. When 60-95% confluent, pBECs growing from the capillary fragments were passaged to permeable membrane filter inserts and established in the models. To increase barrier tightness and BBB characteristic phenotype of pBECs, the cells were treated with the following differentiation factors: membrane permeant 8-CPT-cAMP (here abbreviated cAMP), hydrocortisone, and a phosphodiesterase inhibitor, RO-20-1724 (RO). The procedure was carried out over a period of 9-11 days, and when establishing the NCC model, the astrocytes were cultured 2-8 weeks in advance. Adherence to the described procedures in the protocol has allowed the establishment of endothelial layers with highly restricted paracellular permeability, with the NCC model showing an average transendothelial electrical resistance (TEER) of 1249 &#177; 80 &#937; cm2, and paracellular permeability (Papp) for Lucifer Yellow of 0.90 10-6 &#177; 0.13 10-6 cm sec-1 (mean &#177; SEM, n=55). Further evaluation of this pBEC phenotype showed good expression of the tight junctional proteins claudin 5, ZO-1, occludin and adherens junction protein p120 catenin. The model presented can be used for a range of studies of the BBB in health and disease and, with the highly restrictive paracellular permeability, this model is suitable for studies of transport and intracellular trafficking.

Improved Method for the Establishment of an In Vitro Blood-Brain Barrier Model Based on Porcine Brain Endothelial Cells

The aim of the protocol is to present an optimized procedure for the establishment of an in vitro blood-brain barrier (BBB) model based on primary porcine brain endothelial cells (pBECs). The model shows high reproducibility, high tightness, and is suitable for studies of transport and intracellular trafficking in drug discovery.

The aim of this protocol presents an optimized procedure for the purification and cultivation of pBECs and to establish in vitro blood-brain barrier (BBB) ...

Trans-Tympanic Drug Delivery for the Treatment of Ototoxicity

The systemic administration of protective agents to treat drug-induced ototoxicity is limited by the possibility that these protective agents could interfere with the chemotherapeutic efficacy of the primary drugs. This is especially true for the drug cisplatin, whose anticancer actions are attenuated by antioxidants which provide adequate protection against hearing loss. Other current or potential otoprotective agents could pose a similar problem, if administered systemically. The application of various biologicals or protective agents directly to the cochlea would allow for high levels of these agents locally with limited systemic side effects. In this report, we demonstrate a trans-tympanic method of delivery of various drugs or biological reagents to the cochlea, which should enhance basic science research on the cochlea and provide a simple way of directing the use of otoprotective agents in the clinics. This report details a method of trans-tympanic drug delivery and provides examples of how this technique has been used successfully in experimental animals to treat cisplatin ototoxicity.

We present a technique for localized administration of drugs through the trans-tympanic route into the cochlea. Drug delivery through this route would not interfere with the anti-cancer efficacy of the chemotherapeutic drugs such as cisplatin.

The systemic administration of protective agents to treat drug-induced ototoxicity is limited by the possibility that these protective agents could ...

A Rat Carotid Artery Pressure-Controlled Segmental Balloon Injury with Periadventitial Therapeutic Application

Cardiovascular disease remains the leading cause of death and disability worldwide, in part due to atherosclerosis. Atherosclerotic plaque narrows the luminal surface area in arteries thereby reducing adequate blood flow to organs and distal tissues. Clinically, revascularization procedures such as balloon angioplasty with or without stent placement aim to restore blood flow. Although these procedures reestablish blood flow by reducing plaque burden, they damage the vessel wall, which initiates the arterial healing response. The prolonged healing response causes arterial restenosis, or re-narrowing, ultimately limiting the long-term success of these revascularization procedures. Therefore, preclinical animal models are integral for analyzing the pathophysiological mechanisms driving restenosis, and provide the opportunity to test novel therapeutic strategies. Murine models are cheaper and easier to operate on than large animal models. Balloon or wire injury are the two commonly accepted injury modalities used in murine models. Balloon injury models in particular mimic the clinical angioplasty procedure and cause adequate damage to the artery for the development of restenosis. Herein we describe the surgical details for performing and histologically analyzing the modified, pressure-controlled rat carotid artery balloon injury model. Additionally, this protocol highlights how local periadventitial application of therapeutics can be used to inhibit neointimal hyperplasia. Lastly, we present light sheet fluorescence microscopy as a novel approach for imaging and visualizing the arterial injury in three-dimensions.

The rat carotid artery balloon injury mimics the clinical angioplasty procedure performed to restore blood flow in atherosclerotic vessels. This model induces the arterial injury response by distending the arterial wall, and denuding the intimal layer of endothelial cells, ultimately causing remodeling and an intimal hyperplastic response.

Cardiovascular disease remains the leading cause of death and disability worldwide, in part due to atherosclerosis. Atherosclerotic plaque narrows the ...

Intratracheal Administration of Dry Powder Formulation in Mice

In the development of inhalable dry powder formulations, it is essential to evaluate their biological activities in preclinical animal models. This paper introduces a noninvasive method of intratracheal delivery of dry powder formulation in mice. A dry powder loading device that consists of a 200 &#181;L gel loading pipette tip connected to an 1 mL syringe via a three-way stopcock is presented. A small amount of dry powder (1-2 mg) is loaded into the pipette tip and dispersed by 0.6 mL of air in the syringe. Because pipette tips are disposable and inexpensive, different dry powder formulations can be loaded into different tips in advance. Various formulations can be evaluated in the same animal experiment without device cleaning and dose refilling, thereby saving time and eliminating the risk of cross-contamination from residual powder. The extent of powder dispersion can be inspected by the amount of powder remaining in the pipette tip. A protocol of intubation in mouse with a custom-made light source and a guiding cannula is included. Proper intubation is one of the key factors that influences the intratracheal delivery of dry powder formulation to the deep lung region of the mouse.

Dry powder formulations for inhalation have great potential in treating respiratory diseases. Before entering human studies, it is necessary to evaluate the efficacy of the dry powder formulation in preclinical studies. A simple and noninvasive method of the administration of dry powder in mice through the intratracheal route is presented.

In the development of inhalable dry powder formulations, it is essential to evaluate their biological activities in preclinical animal models. This paper ...

Direct Drug Delivery to Kidney via the Renal Artery

There is a need for directed injections to enable increased and specific renal exposure for efficient evaluation of drug targets in the renal research field. Accumulation of drugs in certain organs may give rise to adverse and unwanted effects, depending on the nature of injectate. To minimize spillover and/or accumulation in other tissues, the herein described method directs the formulation into the renal artery bloodstream by inserting a catheter in the infra renal aorta, just below where it branches into the renal artery, resulting in the kidney as first reached organ and distributing of formulation throughout the kidney.
This manuscript provides a detailed description of the method, as well as its challenges and difficulties. It guides the experimenter to become skillful with this type of microsurgery that requires accuracy under sterile conditions. Speed is crucial for minimizing the ischemia and practicing the procedure will increase the chance of successful injections without adverse effects. By modulating the time between injection and reperfusion as well as the injected volume, the risk of spillover to other organs is mitigated. 
Note that this technique is suitable for single dosing strategies.

This manuscript describes a method for targeted delivery to a single kidney via a catheter placed in the infrarenal abdominal aorta in the mouse.

There is a need for directed injections to enable increased and specific renal exposure for efficient evaluation of drug targets in the renal research ...