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Investigating central nervous system (CNS) diseases is notoriously challenging due to the complex, multimodal intercellular signaling mediated by the interstitial fluid (ISF)1,2,3,4. This complexity is particularly pronounced in brain tumors, such as glioblastoma (GBM), where intercellular signals are conveyed between both neoplastic and stromal cells5,6,7,8,9. In many cases, the aberrant exchange of diverse biomolecules, including metabolites and proteinaceous messengers, contributes to the underlying etiology of CNS pathologies. This investigational challenge is exacerbated, particularly in GBM, by the fact that the molecular composition of ISF is temporally dynamic and evolves throughout disease progression as well as in response to interventional treatments10,11.
Traditional preclinical GBM investigation methods include in vitro studies and single-endpoint animal models. The nature of these approaches limits their broader clinical applicability due to their inability to capture both the characteristics of the tumor microenvironment and longitudinal temporal changes. Advancements made in the early 1980s overcame these contextual limitations with the development of intracerebral microdialysis (cMD)12,13,14,15. Since its inception 45 years ago, cMD has established itself as the standard method for longitudinal sampling of interstitial fluid (ISF) within the living brain16. This is accomplished through the free diffusion and convection of high-concentration ISF solutes through a semipermeable membrane into a continually flowing, low-solute-concentration perfusate, typically artificial cerebrospinal fluid (aCSF)17. These semipermeable membranes are composed of various biocompatible polymers with common molecular-weight pore size cutoffs ranging from 20 kDa to 3 MDa18. This minimally invasive procedure enables the longitudinal in situ collection of a diverse array of analytes, ranging from small molecules, such as metabolites or neurotransmitters, up to large proteins, such as antibodies. However, the structural porosity of cMD membranes coupled with the adsorptive nature of its compositional polymers can significantly impact the relative recovery of analytes with particular biochemical or dimensional characteristics, such as lipids or antibodies, respectively19,20.
Advancements to overcome this limitation of cMD membranes began in the early 2010s with the development of cerebral open-flow microperfusion (cOFM)21. Functioning under similar general principles as cMD, cOFM removes biochemical limitations imposed by semipermeable membranes by exchanging them for a plastic-lattice probe with low-adsorption macroscopic openings of approximately 100 µm size20. A multitude of reports have demonstrated the improved utility of cOFM over cMD through the collection of detectable ISF components, including peptide hormones, nanobodies/antibodies, small lipophilic therapeutics, and PEGylated liposomes19,22,23,24,25. Prior reports examining the physiologic tissue reaction to cOFM guide probe implantation show that blood-brain barrier integrity is re-established by 15 days post-implantation, and that no glial scarring is formed up to 30 days post-implantation26. Due to the replacement of microdialysis membranes with macroscopic openings, investigators have also demonstrated the innovative capacity of cOFM guide probes to facilitate the injection of xenografted glioma cells into the brains of immunodeficient rats, such that atraumatic tumor engraftment and growth occur directly around cOFM sampling area27.
Considerations in the use of cOFM in the study of CNS pathologies must still acknowledge its methodological limitations. Owing to its reliance on the passive diffusion and convection of ISF analytes into a flowing perfusate, these limitations revolve around analyte concentration and sample volume18. Sampled ISF components will be diluted within the collected cOFM perfusate compared to endogenous levels, leading many investigations to compare relative analyte ratios between experimental conditions28. Typical flow rates range from 0.1 µL/min to 1.0 µL/min, equivalent to only 6 µL/h to 60 µL/h. When accounting for tubing dead-space clearance times, the total sampling duration should also be considered. This is particularly important when performing cOFM collections in anesthetized animals, where animal welfare concerns must be carefully addressed. A more detailed description of these and other considerations is available in a previous methods report from the cOFM development team29.
In this manuscript, we provide an updated protocol for employing longitudinal cOFM sampling in the study of neurologic disease, with a focus on GBM. The protocol includes steps for cOFM guide cannula implantation, tumor cell injection, and engraftment through the cOFM guide, as well as two cOFM sampling configurations in awake, freely moving animals. We present representative data demonstrating treatment effects on metabolomic and proteomic ISF components measured by cOFM, the impact of sampling configuration on analyte concentrations, and the efficacy of cOFM-guided tumor cell implantation.