Predicting the Volume of Tissue Activated via Electrode Impedance during Deep Brain Stimulation

2011 ◽  
Author(s):  
Wei-Yi Chuang ◽  
Paul C.-P. Chao ◽  
Kuu-Young Young
Keyword(s):  
Deep Brain Stimulation ◽  
Brain Stimulation ◽  
Electrode Impedance ◽  
Deep Brain

Deep brain stimulation hardware complications: The role of electrode impedance and current measurements

2008 ◽  
Vol 23 (5) ◽  
pp. 755-760 ◽  
Author(s):  
Sierra Farris ◽  
Jerrold Vitek ◽  
Monique L. Giroux
Keyword(s):  
Deep Brain Stimulation ◽  
Brain Stimulation ◽  
Electrode Impedance ◽  
Hardware Complications ◽  
Deep Brain

Anatomic correlates of deep brain stimulation electrode impedance

2014 ◽  
Vol 86 (4) ◽  
pp. 398-403 ◽  
Author(s):  
David Satzer ◽  
Eric W Maurer ◽  
David Lanctin ◽  
Weihua Guan ◽  
Aviva Abosch
Keyword(s):  
Deep Brain Stimulation ◽  
Brain Stimulation ◽  
Electrode Impedance ◽  
Deep Brain Stimulation Electrode ◽  
Stimulation Electrode ◽  
Deep Brain

scholarly journals Sources and effects of electrode impedance during deep brain stimulation

2006 ◽  
Vol 117 (2) ◽  
pp. 447-454 ◽  
Author(s):  
Christopher R. Butson ◽  
Christopher B. Maks ◽  
Cameron C. McIntyre
Keyword(s):  
Deep Brain Stimulation ◽  
Brain Stimulation ◽  
Electrode Impedance ◽  
Deep Brain

scholarly journals Impedance detection of the electrical resistivity of the wound tissue around deep brain stimulation electrodes permits registration of the encapsulation process in a rat model

2019 ◽  
Vol 8 (1) ◽  
pp. 11-24 ◽  
Author(s):  
Kathrin Badstübner ◽  
Marco Stubbe ◽  
Thomas Kröger ◽  
Eilhard Mix ◽  
Jan Gimsa
Keyword(s):  
Deep Brain Stimulation ◽  
Brain Stimulation ◽  
Electrical Impedance Spectroscopy ◽  
Bipolar Electrode ◽  
Electrode Impedance ◽  
Custom Made ◽  
Encapsulation Process ◽  
Deep Brain ◽  
Wound Tissue

Abstract An animal model of deep brain stimulation (DBS) was used in in vivo studies of the encapsulation process of custom-made platinum/iridium microelectrodes in the subthalamic nucleus of hemiparkinsonian rats via electrical impedance spectroscopy. Two electrode types with 100-μm bared tips were used: i) a unipolar electrode with a 200-μm diameter and a subcutaneous gold wire counter electrode and ii) a bipolar electrode with two parallelshifted 125-μm wires. Miniaturized current-controlled pulse generators (130 Hz, 200 μA, 60 μs) enabled chronic DBS of the freely moving animals. A phenomenological electrical model enabled recalculation of the resistivity of the wound tissue around the electrodes from daily in vivo recordings of the electrode impedance over two weeks. In contrast to the commonly used 1 kHz impedance, the resistivity is independent of frequency, electrode properties, and current density. It represents the ionic DC properties of the tissue. Significant resistivity changes were detected with a characteristic decrease at approximately the 2nd day after implantation. The maximum resistivity was reached before electrical stimulation was initiated on the 8th day, which resulted in a decrease in resistivity. Compared with the unipolar electrodes, the bipolar electrodes exhibited an increased sensitivity for the tissue resistivity.

scholarly journals Advancing Directional Deep Brain Stimulation Array Technology

2019 ◽  
Author(s):  
Julia P. Slopsema ◽  
Robert Cass ◽  
Mark Hjelle ◽  
Matthew D. Johnson
Keyword(s):  
Deep Brain Stimulation ◽  
Brain Stimulation ◽  
Electrode Array ◽  
Electrode Impedance ◽  
Before And After ◽  
Optimal Target ◽  
Clinical Interest ◽  
Channel Electrode ◽  
The Brain ◽  
Deep Brain

The degree to which deep brain stimulation (DBS) therapy can effectively treat various brain disorders depends on how well one can selectively stimulate one or more axonal pathways within the brain. There is rapidly growing clinical interest in DBS lead implant designs with electrode arrangements that can better target axonal pathways of interest, especially in cases where the optimal target is immediately adjacent to a pathway that when stimulated will elicit adverse side effects. Numerical modeling has demonstrated that DBS leads with four radially segmented electrodes provide the best balance of directional targeting capability while minimizing the overall number of electrode contacts [1]. Here, we present a novel 4×4 DBS lead (16-channel electrode array) with the same form factor and materials as current 4 or 8-channel FDA-approved DBS leads. Electrode impedance spectroscopy was performed for three of these 4×4 DBS leads showing reliable electrode impedances before and after implantation within the brain.

Electric Field Distribution around the Deep Brain Stimulation Electrode Inferred from Dielectric Measurements

2012 ◽  
Vol 730-732 ◽  
pp. 26-31
Author(s):  
Bogdan Neagu ◽  
Eugen R. Neagu ◽  
Rui Igreja ◽  
C.J. Dias
Keyword(s):  
Deep Brain Stimulation ◽  
Electric Field ◽  
Uniform Distribution ◽  
Brain Stimulation ◽  
Electric Field Distribution ◽  
Electrode Impedance ◽  
Model Calculations ◽  
Deep Brain Stimulation Electrode ◽  
Stimulation Electrode ◽  
Deep Brain

Information about the spatial distribution of the electric field can be obtained by measuring the electrode impedance as a function of the diameter of the electrolyte surrounding the electrode. The non-uniform distribution of the electric field around the electrode is supported by the variation of the geometry factor (GF) with the electrical conductivity and geometry of the volume conductor. A comparison of the values obtained for the GF from experimental data, from model calculations and simulations help to understand the non-uniform distribution of the electric field. The GF calculated from four-electrode-measurements is significantly higher. GF should be used with caution in calculations of the deep brain stimulation (DBS) electrode impedance.

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