the present invention provides leads , sized in some embodiments such that it can be delivered via a percutaneously placed needle , for example , smaller than 12 gauge , typically between 13 and 28 gauge . the lead distal end or distal portion can have at least one flat face . electrodes may be disposed on at least one of the flat faces and can have a flat surface in some embodiments of the invention . the electrode metal substrate can be a corrosion resistant , biocompatible and biostable material , such as platinum , platinum alloys , titanium or titanium alloy , gold , etc . the lead can have 1 or more electrodes ( preferably 1 - 32 and more preferably 4 - 8 electrodes ), with electrical conductors connecting the distal and proximal regions and / or ends , with the proximal region and / or end containing the corresponding number of contacts and configured to be compatible to an implanted pulse generator , or other power source . the electrode dimensions are optimized for battery life by minimizing current loss into undesirable tissue . the insulation of the lead body , and distal and proximal ends , can be a biocompatible and biostable polymer , such as polyurethane , silicone , polyurethane - silicone hybrid , peek ™, polyimide , etc . fig1 shows one lead 20 according to the present invention , having a polymeric distal region 24 including a housing 40 having four flat surface planar electrodes 30 , 32 , 34 , and 36 disposed within a substantially flat housing region 28 . electrical conductors 42 may be seen in a cutout view extending proximally . lead 20 terminates in this embodiment in a somewhat rounded distal end 26 . fig2 illustrates another lead embodiment 120 having a width of less than 2 mm , here about 1 . 3 mm , indicated at 144 , and having electrodes 130 , 132 , and 134 with a surface area of less than about 3 square mm , here about 2 square mm . lead 120 terminates in a distal tip 126 . fig3 illustrates lead 120 of fig2 in cross section , having a thickness of less than about 1 mm , here about 0 . 75 mm , indicated at 146 . housing 148 houses a first electrode 130 having a conductor layer and a surface coating or layer 152 & gt ; which can include a hydrophilic material , steroid , and / or a gaba agonist . a second electrode 132 having a conductor layer 154 with a coating 156 is also shown . fig4 illustrates lead electrode 133 , having a flat metal substrate 150 coated with a hydrophilic layer 152 . fig5 illustrates a neurological stimulation lead 220 according to the present invention . lead 220 can incorporate a multiconductor cable . lead 220 has a distal region 224 a proximal region 226 and an intermediate region 228 disposed between the distal and proximal regions . in a preferred embodiment , the intermediate region is defined to lie between the innermost distal and proximal electrical contacts described below . lead 220 can be formed of a body or shaft 234 extending between a distal end 230 and a proximal end 232 . lead body 234 has an exterior surface or side wall 236 . in some embodiments , the lead body proximal of the distal region has a substantially round cross section , while in other embodiments the lead regions proximal of the distal region are flat on at least one side , similar to the shape of the distal region bearing the electrodes . lead body 234 is preferably formed of a polymeric material , for example , polyurethane or silicone . lead distal region 224 may include a number of electrodes 238 , which may , for example , be cathodes disposed along the bottom of lead body 234 in a spaced - apart configuration . electrodes 238 may also be described as electrical contacts . electrodes 238 are normally adapted to be inserted into the human body , are externally exposed , and can be used for neurological stimulation . one exemplary use of electrodes 238 is the stimulation of the nerves within the spinal cord . proximal region 226 can include a number of connector bands or connector rings 240 disposed in a spaced - apart configuration . connectors 240 may also be described as electrical contacts or terminals , and are preferably also externally exposed . connectors may be circumferential or flat , and may be made from platinum , platinum alloys , stainless steel , nickel alloys , etc . electrodes 238 and connectors 240 may be formed of platinum and / or iridium . connectors 240 can be used for connecting lead 220 to a lead extension to extend the effective length of the lead . in some uses , connectors 240 may also be used to directly couple lead 220 to an implantable pulse generator . electrodes 238 and connectors 240 can be coupled to each other in a one - to - one arrangement . in some leads , the distal - most electrode is coupled to the distal - most connector , the second - to - distal - most electrode coupled to the second - to - distal - most connector , and so forth . the electrodes and connectors can be coupled through conductors extending between the two . in some leads , the conductors are embedded within the lead while in other leads , the conductors lie within lumens extending the length of the lead . in some leads , the conductors are disposed within lumens that are later backfilled to substantially fill the lumens with a polymeric material . some leads have stylet lumens for receiving a stiffening stylet member . lead 220 can be varied in outer diameter and length to suit the application for which it is intended . in some embodiments , lead 220 has a total length of between about 5 cm and about 100 cm . in other embodiments , lead 220 has an outer diameter of less than about 1 mm and a total length of between about 10 cm and 150 cm . uses for the present invention include , but are not limited to : spinal cord stimulation ; brain stimulation ; any central nervous system stimulation ; any peripheral nerve stimulation ; including but not limited to occipital , orbital , cranial , sacral , pudendal , vagus , and / or radial nerves , cardiac pacing and / or defibrillation ; smooth muscle stimulation ( stomach , liver , etc ); and skeletal muscle stimulation . leads according to the present invention can be introduced into the epidural space and used to stimulate the spinal cord . in another use , a lead can be introduced into the intrathecal space for spinal cord stimulation . while not wishing to be bound by theory , applicants believe that intrathecal stimulation is not currently used because circumferential electrodes would dump too much current into the highly conductive cerebral spinal fluid . highly directional electrodes of some embodiments of the present invention , placed in close proximity to the spinal cord , may require much lower current . in some embodiment methods , a gaba agonist coating or layer on the lead distal region : for example , on the electrode , can be placed much closer to the spinal cord when the lead is placed in the intrathecal space . this close proximity to the nerves may increase the effectiveness of the gaba agonist . the gaba agonist coating or coating may also be used in peripheral nerve stimulation . applicants believe peripheral nerve stimulation may also benefit from the close proximity of the electrode and drug to the nerve . various examples and embodiments of the present invention have been presented above , and are intended to illustrate some aspects of the present invention . the scope of the present invention is to be defined by the claims which follow .
devices and methods for stimulating nerves , such as peripheral nerves are described . some devices can include small cross - section lead bodies having one or more electrodes in the round distal portion , the electrodes having a substantially planar surface within the distal portion of the lead which is suitable for placement through a cylindrical needle intended to access a spinal region of a patient . some lead electrodes are covered with a hydrophilic coating at least about 0 . 001 inches thick . the hydrophilic coating may include a steroid and / or a gaba agonist which can elute or diffuse over time , away from the electrode .