Abstract

Flow back along a needle track (backflow) can be a problem during direct infusion, e.g. convection-enhanced delivery (CED), of drugs into soft tissues such as brain. In this study, the effect of needle insertion speed on local tissue injury and backflow was evaluated in vivo in the rat brain. Needles were introduced at three insertion speeds (0.2, 2, and 10 mm/s) followed by CED of Evans blue albumin (EBA) tracer. Holes left in tissue slices were used to reconstruct penetration damage. These measurements were also input into a hyperelastic model to estimate radial stress at the needle-tissue interface (pre-stress) before infusion. Fast insertion speeds were found to produce more tissue bleeding and disruption; average hole area at 10 mm/s was 1.87-fold the area at 0.2 mm/s. Hole measurements also differed at two fixation time points after needle retraction, 10 and 25 min, indicating that pre-stresses are influenced by time-dependent tissue swelling. Calculated pre-stresses were compressive (0 to 485 Pa) and varied along the length of the needle with smaller average values within white matter (116 Pa) than gray matter (301 Pa) regions. Average pre-stress at 0.2 mm/s (351.7 Pa) was calculated to be 1.46-fold the value at 10 mm/s. For CED backflow experiments (0.5, 1, and 2 µL/min), measured EBA backflow increased as much as 2.46-fold between 10 and 0.2 mm/s insertion speeds. Thus, insertion rate-dependent damage and changes in pre-stress were found to directly contribute to the extent of backflow, with slower insertion resulting in less damage and improved targeting.

Highlights

  • Successful treatment of neurological disorders requires effective techniques to deliver drugs to the central nervous system (CNS)

  • For infusions performed with needle insertion speeds of 2 and 10 mm/s, a second small peak (PB in Figure 6A) between 0.2 and 2.46 kPa greater than the local minimum value (PA) was observed

  • Hole measurements were small in the cortex, and no substantial bleeding was observed in the cortex except when it was produced during dura mater removal

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Summary

Introduction

Successful treatment of neurological disorders requires effective techniques to deliver drugs to the central nervous system (CNS). In CED, a cannula (needle) is inserted directly into the parenchyma, and drug infusate is delivered at controlled flow rates into the extracellular space. Infusate flows back along the outer needle wall instead of penetrating into tissue at the needle tip This backflow phenomenon is normally undesirable since large tissue distributions are not achieved, and drugs can reach regions of the brain where they are unintended, not effective, or toxic, resulting in unwarranted side effects [5,6]. Improper targeting has been implicated as one of the most significant barriers to successful implementation of CED in previous clinical brain tumor trials [6,7] In these trials, high rates of ineffective delivery resulted in the majority of infusate leaking into CSF spaces [5,8]. Research has focused on developing new cannula designs [10,11,12], imaging to identify backflow in real-time [13,14,15,16,17,18], and on modeling to predict the extent of backflow [19,20,21]

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