- •Drug Product Development for the Back of the Eye
- •Preface
- •Contents
- •Contributors
- •1.1 Introduction
- •1.2 A Strategic Overview of Drug Delivery Systems
- •1.3 Specific Approaches to Drug Delivery for the Posterior Segment
- •1.3.1 The Influence of Physicochemical Properties on Drug Delivery and Pharmacokinetics
- •1.3.2 The Chosen Route of Administration
- •1.3.3 Location of the Target Tissue
- •1.3.4 Potency of the Drug
- •1.3.5 Need for Continuous or Pulsatile Delivery
- •1.3.6 Duration of Drug Delivery Necessary to Induce and Maintain Efficacy
- •1.3.7 Type of Drug Delivery System Selected
- •1.3.8 Pharmacokinetic (PK) Properties of the Drug
- •1.3.9 Local and Systemic Toxicity of the Drug and its Metabolites
- •1.3.10 Previous Ocular Use of Excipients
- •1.3.11 Development and Strategic Team Input
- •References
- •2.1 Introduction
- •2.2 Posterior Segment as a Sampling Site
- •2.3 Principle of Microdialysis
- •2.3.1 Extraction Efficiency/Recovery
- •2.4.1 Anesthetized Animal Models
- •2.4.2 Conscious Animal Model
- •2.5 Vitreal Pharmacokinetics in Animals Other than Rabbits
- •2.6 Summary
- •References
- •3.1 Commercial Fluorophotometer
- •3.2 Normal Human Subject and Rabbit Ocular Fluorescence
- •3.3 Fluorophotometry Applications
- •3.3.1 Tear Turnover Rate (%/min)
- •3.3.2 Corneal Epithelial Cell Layer Permeability Methodologies
- •3.3.3 Eye Bath Technique
- •3.3.4 Single Drop Technique to Measure Epithelial Permeability
- •3.3.5 Eye Bath Technique to Measure Epithelial Permeability
- •3.4 Clinical Applications of Fluorophotometry
- •3.5.1 Transscleral Pathways
- •3.5.2 Suprachoroidal Injection
- •3.6 Retrobulbar Fluorescein Injection
- •3.7 Intravenous Fluorescein Injection In Vivo
- •3.8 Ocular Uptake of Fluorescein from Topical Eye Drops
- •References
- •4.1 Introduction
- •4.1.1 Role of the Blood-Retinal Barrier as a Dynamic Interface
- •4.1.2 Potential Approach of Blood-Retinal Barrier-Targeted Systemic Drug Delivery to the Retina
- •4.2.1 Amino Acid-Mimetic Drugs
- •4.2.2 Monocarboxylic Drugs
- •4.2.3 Nucleoside Analogs
- •4.2.4 Folate Analogs
- •4.2.5 Organic Cationic Drugs
- •4.2.6 Opioid Peptides and Peptidomimetic Drugs
- •4.2.7 Antioxidants
- •4.2.7.1 Vitamin C
- •4.2.7.2 Vitamin E
- •4.2.7.3 Cystine
- •4.2.8 Miscellaneous Protective Compounds
- •4.2.8.1 Creatine
- •4.2.8.2 Taurine
- •4.3.1 Organic Anion Transporter 3 (OAT3, SLC22A8)
- •4.3.3 P-Glycoprotein (ABCB1)
- •4.3.4 Multidrug Resistance-Associated Proteins (ABCCs)
- •4.3.6 ABCAs
- •4.4 Conclusions and Perspectives
- •References
- •5.1 Introduction
- •5.2 Drug Distribution
- •5.2.1 Drug Distribution from the Anterior Ocular Surface to the Posterior Segment
- •5.2.2 Studies of Trans-Corneal and Periocular Drug Delivery to the Retina
- •5.2.2.1 The Uvea-Scleral Route
- •5.3 Eye Drops for Posterior Segment Diseases in the Clinic
- •5.4 Summary
- •References
- •6.1 Introduction
- •6.2 Vitreous Anatomy
- •6.2.1 The Inner Limiting Membrane
- •6.3 The Vitreous As a Drug Reservoir
- •6.4 Flow Processes in the Vitreous
- •6.4.1 Flow Patterns
- •6.4.2 Injection and Hydrostatic Effects
- •6.4.3 Diffusion
- •6.4.4 Convective Flow
- •6.5 Clearance Pathways from the Vitreous Compartment
- •6.5.1 Charge and Collagen Interaction
- •6.5.2 Aqueous Clearance
- •6.5.3 Retinal Clearance
- •6.6 Transfer Through the Vitreoretinal Border
- •6.6.1 The Role of the Blood–Retinal Barrier
- •6.6.1.1 Amino Acid Transport
- •6.6.1.2 P-Glycoprotein
- •6.6.1.3 Organic Cationic Transporters
- •6.6.1.4 Organic Anion Transporters
- •6.6.1.5 Other Transporters
- •6.7 The Ageing Vitreous
- •6.7.1 Underlying Mechanisms of Vitreous Degeneration
- •6.7.2 Physical Changes Involved in the Ageing Vitreous
- •6.7.2.1 Pre-Clinical Model of Ageing Vitreous
- •6.7.2.2 Effects of Vitreous Liquefaction on Intravitreal Drug Delivery
- •6.7.3 Vitrectomised Eyes
- •6.7.3.1 Intravitreal Drug Distribution and Clearance in Silicone Oil
- •6.7.4 Role of Ocular Movements in Disordered Vitreous
- •6.8 Concluding Remarks
- •References
- •7.1 Introduction
- •7.2 Drug Delivery to Posterior Segment Ocular Tissues
- •7.3 Scleral Structure and Drug Delivery
- •7.4 Scleral Permeability: Initial Studies
- •7.5 Sustained-Release Delivery In Vitro
- •7.6 In Vivo Studies
- •7.7 Conclusions and Future Directions
- •References
- •8.1 Introduction
- •8.2 Background
- •8.3 Posterior Segment Delivery
- •8.4 Transscleral and Intrascleral Drug Delivery
- •8.5 Suprachoroidal Drug Delivery
- •8.6 Summary
- •References
- •9.1 Introduction
- •9.2 Nonbiodegradable Ocular Drug Delivery Systems
- •9.2.1 Retisert
- •9.2.2 Ocusert
- •9.2.3 Vitrasert
- •9.2.4 I-vation
- •9.2.5 Iluvien
- •9.2.6 Nonbiodegradable Matrix Implants
- •9.2.6.2 Punctal Plugs
- •9.3 Medical Applications for Biodegradable Polymers
- •9.3.3 Poly(Ortho Esters)
- •9.3.4 Polyanhydrides
- •9.5.1 Ozurdex™
- •9.5.2 Surodex
- •9.5.3 Verisome
- •9.5.4 Lacrisert
- •9.6.1 Poly(Lactic Acid)-Based Implants
- •9.6.2 PLGA-Based Implants
- •9.6.5 Poly(Ortho Ester)-Based Implants
- •9.6.6 Polyanhydride-Based Implants
- •9.6.7 Other Biodegradable Polymer-Based Implants
- •9.7 Conclusions
- •References
- •10.1 Introduction
- •10.2 Manufacturing of Microparticles
- •10.3 Characterization of Microparticles
- •10.3.1 Morphological Characterization of Microparticles
- •10.3.2 Particle Size Analysis and Distribution
- •10.3.3 Infrared Absorption Spectrophotometry (IR)
- •10.3.4 Differential Scanning Calorimetry (DSC)
- •10.3.5 X-Ray Diffraction
- •10.3.6 Gel Permeation Chromatography (GPC)
- •10.3.7 Determination of Drug Loading Efficiency
- •10.3.8 “In Vitro” Release Studies
- •10.3.8.1 Additives in Microspheres
- •10.4 Sterilization of Microparticles
- •10.5 Calculation of the Dose of Microparticles for Injection
- •10.6 Injectability Studies
- •10.7 In Vivo Studies
- •10.7.1 In Vivo Injection of Microparticles
- •10.7.2 Ocular Disposition and Cellular Uptake
- •10.7.3 Tolerance of Microparticles
- •10.7.4 In Vivo Degradation of PLA and PLGA Microparticles
- •10.8 In Vitro and In Vivo Correlation
- •10.9 Microparticles for the Treatment of Posterior Segment Diseases. Animal Models and Human Studies
- •10.9.1 Proliferative Vitreoretinopathy (PVR)
- •10.9.2 Uveitis
- •10.9.3 Age-Related Macular Degeneration (AMD)
- •10.9.4 Diabetic Retinopathy
- •10.9.5 Macular edema
- •10.9.6 Acute Retinal Necrosis (ARN)
- •10.9.7 Cytomegalovirus (CMV) Retinitis
- •10.9.8 Choroidal Neovascularization
- •10.9.9 Diseases Affecting the Optic Nerve
- •10.9.11 Microparticles in Retinal Repair
- •10.10 Conclusions
- •References
- •11.1 Introduction
- •11.2 Nanoparticles
- •11.2.1 Polymer Nanoparticles
- •11.2.2 Liposomes and Lipid Nanoparticles
- •11.2.3 Micelles
- •11.2.4 Protein Nanoparticles
- •11.2.5 Carbohydrate Nanoparticles
- •11.2.6 Dendrimers
- •11.2.7 Combination Nanosystems
- •11.3 Using Nanotechnology to Improve Ocular Therapeutics
- •11.3.1 Improving Patient Compliance
- •11.3.2 Increasing Drug Retention and Sustained Release
- •11.3.3 Increasing Permeability and Tissue Partitioning
- •11.3.4 Targeting Nanotherapies
- •11.3.5 Intracellular Trafficking
- •11.4 Alternative Approaches to Improve Ocular Therapeutics
- •11.5 Conclusion
- •References
- •12.1 Introduction
- •12.2 Hydrogel Technology
- •12.6 Future Directions
- •References
- •13.1 Introduction
- •13.2 General Design Considerations
- •13.2.1 Administration Site
- •13.2.2 Body Design
- •13.2.3 Port Design
- •13.2.4 Vacuum and Pressure
- •13.2.5 Flushing and Fluid Replacement
- •13.2.5.1 Active Pumps
- •13.2.5.2 Passive Systems
- •13.2.5.3 Solid Refill
- •13.2.6 Contamination Potential
- •13.3 Historical Influences
- •13.3.1 Infusion Pumps
- •13.3.2 Glaucoma Drainage Devices
- •13.3.3 Pioneering of Refill Procedure in the Eye
- •13.4 Ophthalmic Refillable Devices
- •13.4.1 Invasiveness and Refilling Frequency
- •13.4.2 Intravitreal Delivery Through the Pars Plana
- •13.4.3 Episcleral Implantation for Trans-Scleral Delivery
- •13.4.4 Subretinal and Suprachoroidal Implantation
- •13.4.5 Lens Capsule Delivery
- •13.5 Conclusions
- •References
- •14.1 Introduction
- •14.2 Current Methods of Drug Delivery to the Eye
- •14.3 Improved Methods of Drug Delivery to the Eye Using Microneedles
- •14.3.1 Intrastromal Delivery to the Cornea Using Coated Microneedles
- •14.3.3 Suprachoroidal Delivery Using Hollow Microneedles
- •14.4 Microneedle Types and Other Applications
- •14.4.1 Poke and Apply
- •14.4.2 Coat and Poke
- •14.4.3 Poke and Release
- •14.4.4 Poke and Flow
- •14.5 Discussion
- •14.6 Conclusion
- •References
- •15.1 Introduction
- •15.1.1 General Mechanisms of Iontophoretic Drug Delivery
- •15.1.2 The Shunt Pathway
- •15.1.3 The Flip–Flop Gating Mechanism
- •15.1.4 Electro-Osmosis
- •15.2 Ocular Drug Delivery: The Past and the Future
- •15.3 Ophthalmic Applications of Iontophoresis
- •15.3.1 Transconjunctival Iontophoresis
- •15.3.1.1 Transconjunctival Iontophoresis of Antimitotics
- •15.3.1.2 Transconjunctival Iontophoresis of Anesthetics
- •15.3.2 Transcorneal Iontophoresis
- •15.3.2.1 Transcorneal of Fluorescein Iontophoresis for Aqueous Humor Dynamic Studies
- •15.3.2.2 Transcorneal Iontophoresis of Antibiotics
- •15.3.2.3 Transcorneal Iontophoresis of Antiviral Drugs
- •15.3.2.4 Other Drugs for Transcorneal Iontophoresis
- •15.3.2.5 Is Transcorneal Iontophoresis Safe?
- •15.4 Transscleral Iontophoresis
- •15.4.1 Transscleral Iontophoresis of Antibiotics
- •15.4.2 Transscleral Iontophoresis of Antiviral Drugs
- •15.4.3 Transscleral Iontophoresis of Anti-Inflammatory Drugs
- •15.4.3.1 Aspirin
- •15.4.3.2 Glucocorticoids
- •15.4.3.3 Transscleral Iontophoresis of Carboplatin
- •15.4.3.4 Is Transscleral Iontophoresis Safe?
- •15.4.3.5 Transscleral Iontophoresis for High Molecular Weight Compounds and Proteins
- •15.4.3.6 Clinical Application of Transscleral Iontophoresis
- •15.5 Applications of Iontophoresis to Ocular Gene Therapy
- •15.6 Future Developments
- •References
- •16.1 Introduction
- •16.2 Background
- •16.2.1 Intravitreal Injections
- •16.2.2 Impact of Genetics
- •16.3 Better Tools for Delivery and Treatment
- •16.3.1 Barriers to Success
- •16.3.2 Physics-Based Approaches
- •16.3.2.1 Physical Methods to Deliver Drugs to a Target Cell in the Posterior Segment
- •16.3.2.2 History of Electrical Fields in Medicine
- •16.3.2.3 Safety Concerns with Electric Fields
- •16.3.2.4 Definitions of Electric Field Methods
- •16.3.2.5 Advantages of Electric Fields for DNA Transfection vs. Viral Mediated DNA Delivery
- •16.3.2.6 Problems of In Vivo Electric Field Applications
- •16.3.2.7 Possible Strategies to Improve Electric Field-Mediated Drug Delivery
- •16.3.3 Experiences with Iontophoresis
- •16.3.3.1 Examples of Iontophoresis
- •16.3.3.2 Summary of the Strengths and Weaknesses of Iontophoresis
- •16.3.4 Experiences with Electroporation
- •16.3.4.1 Examples of Electroporation in Living Animals
- •16.3.4.2 Strengths and Weaknesses of Electroporation
- •16.4 Outstanding Issues in Electric Fields for the Delivery of Drugs
- •16.5 Summary
- •References
- •17.1 Introduction
- •17.2 Routes of Protein Administration
- •17.2.1 Topical
- •17.2.2 Intracameral
- •17.2.3 Intravitreal
- •17.2.4 Periocular (Transscleral)
- •17.2.5 Suprachoroidal
- •17.2.6 Subretinal
- •17.2.7 Systemic
- •17.3 Advantages and Challenges of Protein Delivery
- •17.4 Current Development Strategies
- •17.4.1 Pure Protein
- •17.4.2 PEGylation
- •17.4.4 Liposomes
- •17.4.5 Stem Cells
- •17.4.6 Implants
- •17.5 Case Studies
- •17.6 Ophthalmic Protein Formulation Development
- •17.6.1 Protein Biosynthesis
- •17.6.2 Preformulation Studies
- •17.6.3 Selection of Excipients
- •17.6.4 Optimization of Process Variables
- •17.7 Specifications and Regulatory Guidelines
- •17.8 Conclusions
- •References
- •18.1 Need for Suspension Development for the Back of the Eye
- •18.2 Background
- •18.3 Development of Drug Suspensions Intended for the Back of the Eye
- •18.3.1 Drug Suspensions
- •18.3.1.1 Physical Pharmacy Principles that Explain the Stability and Formulation of Suspensions
- •18.3.1.2 Formulation Methodology
- •18.3.1.3 Manufacturing Process
- •18.3.2 Factors To Be Considered in Suspension Development for the Back of the Eye
- •18.3.2.1 Formulation Development and Evaluation
- •18.3.2.2 In Situ Forming Suspensions, Selection of Drug Form for Suspension, and Polymeric Microparticle Suspension
- •18.3.2.3 Clinical Studies on Safety
- •18.4 Conclusions
- •References
- •19.1 Introduction
- •19.2 Drug Product Approval Process
- •19.3 Considerations for Back of the Eye Treatments
- •19.4 Adaptive Trial Design
- •19.5 Drug-Device Combinations
- •19.6 Product Summary Basis of Approval Reviews
- •19.6.1 OZURDEX™
- •19.6.2 LUCENTIS™
- •19.7 Summary
- •References
- •20.1 Background
- •20.2 FDA Endpoints
- •20.3 Endpoints for Neovascular Age-Related Macular Degeneration (Table 20.1)
- •20.4 FDA Guidelines for Other Retinal Diseases
- •20.5 Endpoint for Geographic Atrophy
- •20.6 Endpoint for Retinal Vein Occlusion
- •20.7 Future Endpoints
- •References
- •21.1 Introduction
- •21.2 Ocular Physiology and Pathology
- •21.2.1 Ocular Inflammation
- •21.2.2 Neovascularization
- •21.2.3 Degeneration
- •21.3 Current Therapies for Key Back of the Eye Disorders
- •21.3.1 Age-Related Macular Degeneration
- •21.3.1.1 Pathophysiology
- •21.3.1.2 Therapeutics Either in Current Use or in Clinical Trials
- •21.3.1.3 Current Research Focused on Identifying New Targets
- •21.3.2 Diabetic Retinopathy
- •21.3.2.1 Pathophysiology
- •21.3.2.2 Therapeutics Either in Current Use or in Clinical Trials
- •21.3.3 Retinopathy of Prematurity
- •21.3.3.1 Pathophysiology
- •21.3.3.2 Therapeutics Either in Current Use and in Clinical Trials
- •21.3.4 Degenerative Conditions
- •21.3.4.1 Pathophysiology
- •21.3.4.2 Therapeutics Either in Current Use or in Clinical Trials
- •21.3.5 Opportunistic Infections
- •21.3.5.1 Pathophysiology
- •21.3.5.2 Therapeutics Either in Current Use or in Clinical Trials
- •21.3.6 Autoimmune Disease
- •21.3.6.1 Pathophysiology
- •21.3.6.2 Therapeutics Either in Current Use or in Clinical Trials
- •21.4 Conclusion
- •References
- •22.1 Bile Acids as Anti-Apoptotic Neuroprotectants
- •22.3 Potential Need for Local Delivery of Bile Acids as Neuroprotectants
- •22.4 Preliminary Studies of Ocular Delivery of Bile Acids
- •22.5 Conclusion
- •References
- •Index
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22.3 Potential Need for Local Delivery of Bile Acids as Neuroprotectants
It thus appears that systemic routes as a delivery modality may be sufficient in TUDCA or UDCA treatment of posterior ocular disease. Oral delivery of either leads to few and minimal side effects (Parry et al. 2010; Nakagawa et al. 1990; Crosignani et al. 1996; Setchell et al. 1996; Invernizzi et al. 1999), results in elevated serum and plasma levels of UDCA and its conjugates (Batta et al. 1989, 1993; Setchell et al. 1996; Invernizzi et al. 1999; Parry et al. 2010), and clearly slows or prevents retinal damage or degeneration in a number of animal models. However, systemic delivery may not be sufficient due to possible individual variability in response to systemic dosing.
Though TUDCA and UDCA have been approved for treatment liver and gall bladder afflictions for decades, relatively little is known about the pharmacokinetics of these bile acids in normal, diseased, or dosed states (Invernizzi et al. 1999). Studies that do report bile acid levels in blood and non-hepato-biliary tissues generally do not focus on UDCA and its conjugates as these bile acids do not make up a substantial proportion of the bile acid pool in humans. The studies that do report circulating levels of UDCA and its conjugates indicate great variability in serum, plasma, or CSF levels among individuals (Invernizzi et al. 1999; Parry et al. 2010).
There are significant differences in UDCA and TUDCA pharmacokinetics following oral administration. TUDCA administration leads to greater biliary UDCA enrichment than UDCA administration, probably because hepatic extraction of taurine-conjugated bile acids is more efficient than that of their unconjugated forms (Invernizzi et al. 1999). This may result in better clinical efficacy for treatment of hepato-biliary disease. Of added importance in regards to these and other potential therapeutic uses is that TUDCA undergoes much less biotransformation to lithocholic acid than does UDCA (Invernizzi et al. 1999). Lithocholic acid is cytotoxic and there are concerns that a harmful side effect of long-term UDCA treatment can be liver damage (Invernizzi et al. 1999).
Of more direct importance to neuroprotection uses, oral dosing with either UDCA or TUDCA produces high serum concentrations of UDCA conjugates. Oral administration of UDCA results in UDCA and its conjugates becoming the dominant bile acids in biliary bile and absolute concentrations in blood increase over tenfold (Fedorowski et al. 1977; Parquet et al. 1985; Oka et al. 1990; Stiehl et al. 1990; Batta et al. 1993; Rubin et al. 1994). About half of an UDCA dose is absorbed from the portal blood into liver via first pass extraction, where it is conjugated with glycine, forming glycoursodeoxycholic acid (GUDCA), or taurine, forming TUDCA (Nakagawa et al. 1990; Hofmann 1994; Rubin et al. 1994; Paumgartner and Beuers 2002). The percentage absorbed decreases with increasing dose such that absolute and proportional enrichment of the biliary bile with UDCA and conjugates plateaus at an as-yet undefined dose due to epimerization of UDCA to chenodeoxycholic acid (CDCA) and endogenous bile acid synthesis (Tint et al. 1982; Parquet et al. 1985; Walker et al. 1992; Hofmann 1994). UDCA and conjugates are excreted from
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the biliary tree and resorbed through the enterohepatic circulation or metabolized to insoluble salts and excreted in the feces (Rubin et al. 1994). Oral TUDCA produces similar changes in bile acid composition and concentrations, but with higher proportions and concentrations of UDCA and conjugates, possibly due to reduced intestinal biotransformation of TUDCA, suggesting enhanced bioavailability (Crosignani et al. 1996; Setchell et al. 1996).
Though oral dosing with UDCA or TUDCA greatly increases serum levels of UDCA conjugates, bile acid compositions and levels in blood vary greatly across subjects. Oral treatment of PBC patients with either TUDCA or UDCA (750 mg/ day for 2 months) results in higher serum levels of UDCA conjugates, but of great concentration range (Invernizzi et al. 1999). UDCA serum levels were 24.1 ± 15.1 mmol/L (mean ± SD) following UDCA treatment and 26.1 ± 19.9 following TUDCA treatment. (Pretreatment levels were 0.2 ± 0.3 and 0.1 ± 0.2 mmol/L, respectively.) (Invernizzi et al. 1999).
Similar variability was observed in other studies. Feeding UDCA (12–15 mg/kg body weight per day) to PBC patients for 6 months results in UDCA and its conjugates in becoming the most prevalent bile acids both in serum and urine with a corresponding decrease in the endogenous bile acid concentrations, with absolute levels of serum UDCA increasing from 1.7 mmol/L prior to treatment to 24.5 mmol/L. However, serum UDCA concentrations across patients ranged from 2.3 to 51.3 mmol/L, a remarkable variation in response to the same dosing regimen (Batta et al. 1989).
Variability in serum levels following oral UDCA administration may result in differences at neuronal tissue targets. In subjects who are free of known hepatobiliary disease, oral dosing with 15-, 30-, and 50-mg/kg body weight for 29 days led to significantly increased serum UDCA concentrations that correlated with dose concentration and with concentration of UDCA in CSF (Parry et al. 2010). However, for each dose, CSF UDCA concentrations varied greatly (fourfold, 3.5-fold, and 2.7-fold, respectively), suggesting that even in subjects without hepato-biliary compromise, the amount of UDCA “spilled” into the circulation varies greatly from subject to subject.
Where might this variability originate and could it have consequences for the utility of TUDCA or UDCA use as neuroprotectants in the ophthalmic clinic? Several transporters and metabolic enzymes mediate the regulation of endogenous bile acid concentrations in circulation. One of these, organic anion transporting polypeptide 1B1 (OATP1B1), is an influx transporter that mediates hepatic uptake of endogenous compounds such as bile acids and bilirubin and also uptake of several drugs from the portal blood (reviewed in Xiang et al. 2009). Polymorphisms in SLCO1B1, the gene that codes for OATP1B1, are linked to differences in the pharmacokinetics and effects of several drugs. Recently, SLCO1B1 polymorphisms were similarly linked to differences in plasma levels of bilirubin and bile acids, including UDCA and TUDCA (Xiang et al. 2009). In particular, reduced plasma concentrations of UDCA and TUDCA were associated with the SLCO1B1*1B/*1B genotype, leading the study’s authors to suggest that this is likely due to enhanced hepatic uptake mediated by OATP1B1 during enterohepatic circulation (Xiang et al.
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2009). It is of course not clear that processes that regulate fasting levels of bile acids will similarly mediate circulating levels of UDCA and its conjugates during therapeutic intervention. At the dosages given, the regulatory capacity of such mediators may be overwhelmed.
In agreement with these human subject trials, experiments with mouse strains lacking all mouse Oatp1a/1b transporters show markedly increased plasma levels of unconjugated bile acids. These mice also have decreased hepatic uptake and thus increased systemic levels following i.v. or oral administration of the OATP substrate drugs methotrexate and fexofenadine (van de Steeg et al. 2010). It is thus possible that substrates of OATP such as UDCA or TUDCA, when given systemically as drugs, indeed may have their pharmacokinetics mediated by these transporters.
We have observed strain differences in fasting serum levels of TUDCA of mice. Serum of Balb/C mice had very low TUDCA concentrations (0.0293 ± 15 mmol/L, N = 17; mean ± SEM), whereas C57BL/6J mice had easily measured levels, but over a large range (27.4 ± 12 mmol/L, range of 0.007–170 mmol/L; N = 16). However, we have not been able to identify strain-specific polymorphisms in the mouse homolog of SLCO1B1, SLCO1b2, that correspond to those of SLCO1B1 associated with altered circulating bile acid levels in humans (Foster et al. 2009). Obviously numerous other mediators of circulating bile acid levels could be at play here. We continue to explore the source of this strain difference.
22.4 Preliminary Studies of Ocular Delivery of Bile Acids
Individual or subpopulation differences in the regulation of circulating levels of TUDCA and UDCA following systemic administration could confound assessment of their efficacy as neuroprotectants in treatment of posterior ocular disease. Thus, it may be useful to test local delivery. We have initiated such studies and find that a single intravitreal injection of TUDCA provides protection in the LIRD mouse model comparable to that provided by multiple systemic injections reviewed above and elsewhere (Boatright et al. 2006a, b, 2009a).
In these experiments, Balb/C mice were intravitreally injected with 1 mL of varying doses of free acid TUDCA 0.5, 5, 15, 30, 50 mg/mL in phosphate-buffered saline (PBS) in one eye, and with sterile PBS in the other. ERGs were taken weekly. Mice sacrificed at various times after injection to assess morphology and TUNEL signal in retina sections. Doses higher than 5 mg/mL showed reduced a-wave and b-wave amplitudes in the ERG waveforms, and increased apoptotic signal that corresponded to reduced ONL thickness (Kendall et al. 2008). Doses of 5 mg/mL and below, however, showed similar ERG amplitudes to that of the PBS treated eyes, along with similar retinal morphology. Based on this, we tested the effects of a single intravitreal injection on LIRD as described above and elsewhere (Boatright et al. 2006a, b, 2009a). Balb/C mice were intravitreally injected with 1 mL of 5 mg/mL of TUDCA or PBS in each eye, dark-adapted overnight, and exposed to bright light (10,000 lux) or dim light (50 lux) for 7 h on the following day. ERGs were taken
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weekly for 3 weeks after light damage. Dim-adapted ERG a-wave and b-wave amplitudes were greater in eyes that had been injected with TUDCA-treated eyes compared to amplitudes generated by the PBS-injected contralateral eyes. Similarly, TUDCA-treated eyes showed reduced TUNEL signal compared to their PBS counterparts (Kendall et al. 2008). Thus, a single intravitreal injection of 5 mg/mL of TUDCA protected against LIRD.
In addition to intravitreal injection, preliminary data suggests that TUDCA should be able to be delivered transsclerally as it has predictable scleral diffusion parameters. We assessed whether TUDCA in balanced salt solution (BSS) or balanced salt solution plus (BSS+) can diffuse across human sclera. Donor sclera was mounted in a Lucite block perfusion chamber. The outer surface of the sclera was exposed to 200 mL of TUDCA (50 mg/mL) in either BSS or BSS+ for 24 h. Perfusate fractions were collected every 2 h over a 24 h period. Ultra performance liquid chromatography (UPLC)/tandem mass spectrometry was used to quantitate TUDCA and unconjugated UDCA in perfusates. We found that TUDCA readily diffused across sclera. The transscleral permeability constant (Kconst) for TUDCA was 1.89 × 10−6 cm/s in BSS, 1.97 × 10−6 cm/s in BSS+, and 4.63 × 10−7 cm/s in fibrin sealant. These perfusion rates are in agreement with other compounds of similar molecular weight (e.g., penicillin G, Doxil, rhodamine, dexamethasone-fluorescein, etc.) (Boatright et al. 2009b).
22.5 Conclusion
The hydrophilic bile acids UDCA and TUDCA are anti-apoptotic and protective in many neurodegeneration models. Protective effects in ocular disease models are reported by several independent laboratories using models of ADRP, AMD, and other diseases and injuries (Arora et al. 2009; Boatright et al. 2009a). In nearly all of the studies testing in vivo models of neurodegeneration and retinal degeneration, systemic treatment provides marked protection. Such efficacy coupled with the lack of notable side effects in animals or humans suggests that systemic delivery is an adequate delivery modality for these therapeutic compounds. As such, it is worthwhile to consider that the few studies that have directly examined circulating levels of UDCA and its conjugates, either in the resting state or following bile acid therapy, indicate that humans and mice can have vastly differing levels of these bile acids. This variability may be due to individual or subpopulation differences in bile acid physiology and could have ramifications for clinical trial design and eventual neuroprotective therapeutic use, particularly if subpopulations are refractory to attempts to increase circulating levels via systemic administration of these bile acids in order to provide therapeutically sufficient concentrations at target tissues. Local delivery might be required. Our initial experiments testing in vivo intraocular injections and in vitro transscleral permeability indicate that this will be no more challenging than for other ophthalmic therapeutic compounds currently being tested or already in the clinic.
