as required , detailed embodiments of the present invention are disclosed herein ; however , it is to be understood that the disclosed embodiments are merely exemplary of the invention , which may be embodied in various forms . therefore , specific structural and functional details disclosed herein are not to be interpreted as limiting , but merely as a basis for the claims and as a representative basis for teaching one skilled in the art to variously employ the present invention in virtually any appropriately detailed structure . the reference numeral 20 generally refers to a unitized electrode with three - dimensional capabilities for detection and control of brain state changes in accordance with the present invention , as shown in fig6 a through 6f . fig6 a and 6b show an enlarged top and side perspective view and an enlarged bottom and side perspective view , respectively , of an electrode 20 having a “ tack ”- like configuration with a disk portion 22 , a shaft portion 24 , and conductors 26 , such as electrically conducting wires or other suitable arrangement as appropriate for a particular application as hereinafter disclosed . the shaft portion 24 is secured to , or formed integrally with , the disk portion 22 and generally extends perpendicularly outwardly from the disk portion 22 , preferably from the center thereof . for some applications , however , it may be desirable that the shaft portion 24 be spaced off - center and / or at a selected angle relative to the disk portion 22 . the shaft portion 24 is generally inserted in a radial direction , i . e ., parallel to the orientation of apical dendrites or of the fibers ( axons ) entering or leaving the cortex at that site . in some applications , however , the shaft portion 24 may be inserted orthogonally or obliquely into the cortex . the direction of insertion is a function of the site selected for recording or control of brain state changes . this approach is favored over others , such as anchoring the device to the dura mater or to the skull , because it increases the area of recording surfaces and minimizes tearing of the cortex and dura that may result from differential displacement of these structures associated with head movements of certain force / acceleration and direction . the disk portion 22 has an upper surface 28 and a lower surface 30 . the shaft portion 24 has an outer surface 32 . as shown in fig6 a and 6b , the outer surface 32 of the shaft portion 24 has a single recording and / or stimulating contact surface 32 thereon connected in communication with conductor 26 . alternately , the shaft portion 24 may have a plurality of bands of recording and / or stimulating contact surfaces 36 separated by insulating material 38 , as indicated in fig6 d and 6f . in that event , each of the recording and / or stimulating surfaces 36 is independently connected to a different one of the conductors 26 . in addition , the lower surface 30 of the disk portion 22 may have a single recording and / or stimulating contact surface 40 connected in communication with a separate one of the conductors 26 . alternately , the disk portion 22 may have one or more concentric annularly - shaped bands of recording and / or stimulating contact surfaces 42 separated by insulating material 44 , as indicated in fig6 e . in that event , each of the recording and / or stimulating contact surfaces 42 is independently connected to a different one of the conductors 26 and independently of conductors 26 connected to the bands of recording and / or stimulating contact surfaces 36 on the outer surface 32 of shaft portion 24 . for some applications , it may be desirable to use one or more circularly - shaped recording and / or stimulating contact surfaces 46 separated by insulating material 48 in place of some or all of the previously described annularly - shaped bands of recording and / or stimulating contact surfaces 42 , as depicted in fig6 f . generally , the disk portion 22 has a diameter between approximately 1 – 25 mm and the shaft portion 24 has a diameter between approximately 0 . 1 – 1 . 0 mm ; it is to be understood , however , that the disk portion 22 and the shaft portion 24 may have other dimensions as necessary for a particular application . the length of the shaft portion 24 may have any desired length depending on the location as required for a particular application , as shown in fig6 c , wherein one of the electrodes 20 is inserted directly into brain tissue , designated by the numeral 50 , and another one of the electrodes 20 in inserted into a fold of the gyrus , designated by the numeral 52 . fig6 c illustrates how the electrode 20 can be inserted into the fold of the gyrus so that it can record from the unexposed surfaces , which project a negligible solid angle onto electrodes placed on the surface of the cortex . another advantage of electrode 20 is that the arrangement of the disk portion 22 and the shaft portion 24 relative to each other provide each other with the anchoring needed to maintain good contact and stable target acquisition , thereby improving signal - to - noise ratio , detection performance and efficacy of control measures . in other words , electrode 20 may be inserted into the exposed cortex or into the folds to record from both unexposed cortex and from the depths of the cortex . the insertion of the shaft portion 24 either directly into brain tissue or into a fold of the gyrus stabilizes the electrode 20 and prevents undesired lateral movement of the contact surfaces 40 on the lower surface 30 of the disk portion 22 relative to the exposed surface of the cortex which the contact surfaces 40 are bearing against . concurrently therewith , the abutting engagement between the lower surface 30 of the disk portion 22 stabilizes the electrode 20 and prevents undesired axial movement of the contact surfaces 36 of the shaft portion 24 relative to brain tissue . in other words and as one skilled in the art can determine from this disclosure , the presence of disk portion 22 provides supporting and anchoring capabilities to the shaft portion 24 and prevents undue movement of the shaft portion 24 to thereby avoid the consequent noise and contaminated signals as experienced with the use of prior art devices . similarly , the presence of the shaft portion 24 provides an anchor to the contact surfaces of the disk portion 22 to prevent movement artifacts . electrode 20 is sometimes referred to herein as a mesoelectrode because the diameter of the shaft is between the dimensions of the microelectrodes for single unit or intracellular recordings and the depth macro electrodes shown in fig2 . depending on the diameter of the shaft portion 24 , the present invention records activity ranging from minicolums which correspond approximately to 10 2 neurons which constitute a minicolumn ( for diameters of ˜ 0 . 1 mm ) to possibly up to 10 5 – 10 6 neurons which constitute a macrocolumn ; that is , the mesoelectrode of the present invention can simultaneously record activity from multiple spatial scales . those skilled in the art realize that the mesoelectrode electrode can have two or more shaft portions as required for a particular application . the mesoelectrode can be inserted , as shown in 6 a , into the exposed cortex or into the folds of the cortex to record from unexposed cortex and from its depths . this macroelectrode can be used for subcortical structures but not for cortical recordings . an electrode having a tip diameter of 10 − 3 cm and placed closed to the body of a neuron records activity contributed by approximately one hundred neurons . electrode 20 is constructed of biocompatible materials , such as polyurethane covered as appropriate with thin sheets or coatings of noble metals , such as platinum or other suitable material . the shaft portion 24 of the mesoelectrode 20 is configured to operatively accept a rigid mandrel to guide the electrode 20 into the brain tissue . the various contact surfaces are constructed of inert but conductive materials , such as platinum or platinum - iridium or other suitable material . if desired , contact surfaces of the disk portion 22 and shaft portion 24 may be “ printed ” or deposited onto the respective underlying surfaces using photolithographic techniques . in the case of the circularly - shaped contacts 46 shown in fig6 f , the diameter thereof generally ranges between approximately 1 – 5 mm and the contacts of the shaft portion 24 may be of any suitable length . insulating material between the various contact surfaces is constructed of biologically inert material , such as polyurethane or other suitable material , to prevent adjacent contacts from touching each other , which could otherwise create an undesirable “ shunt ”. conductors 26 , passing through the shaft and protruding from the upper surface 28 of the disk portion 22 , transfer signals from the various contact surfaces to amplifiers , usually for recording purposes , and are constructed of electrically conductive material , such as copper or other suitable material . electrical insulation is present about the conductors 26 throughout the shaft portion 24 and continues up to the juncture between the conductors 26 and the corresponding contact surface . conductors or wires 26 may also be used to convey control signals from control units ( or stimulation units ) to selected ones of the contact surfaces . each individual contact surface of the disk portion 22 and shaft portion 24 is connected to an electrically distinct conductor 26 allowing any contact surface to be independently available for stimulation either synchronously or asynchronously . for some applications , it may be desirable that communication to and from the electrode 20 be wireless , through micro - or nano - telemetric devices , housed in , or spaced in close proximity to , the electrode 20 . the presence of the contact surfaces of the disk portion 22 and the shaft portion 24 in three distinct axes provides three - dimensional information gathering capability for brain electrical activity ( bea ) and thus improves over the capabilities of the prior art devices for analysis of brain signals . the presence of multiple contacts on the shaft portion 24 and on the disk portion 22 improves the temporal and spatial resolution of cortical signals and also of the therapy delivered to the cortex , which translate into improved detection and control of brain state changes . the various contact surfaces that are connected to control units through conductors 26 not only allow usage of electrical stimulation strategy but also allow other therapeutic modalities such as cooling . those skilled in the pertinent art will appreciate that the mesoelectrode may be constructed using ceramic or silicon and thin - film techniques . a first modified embodiment of the unitized electrode with three - dimensional capabilities for detection and control of brain state changes , designated by the numeral 60 , is depicted in fig7 . the first modified embodiment 60 includes a hollow body mechanism 61 having one or more retractable electrode devices 62 with distal ends 63 that can be selectively pushed out into the cortex , wherein the body mechanism 61 is secured to a disk portion 64 similar to that hereinbefore described for electrode 20 . disk portion 64 provides supporting and stabilizing structure for the first modified embodiment 60 but can also have one or more recording and stimulating contact surfaces on a lower surface 65 thereof , as hereinbefore described . while the body mechanism 61 is being inserted into a fold of the gyrus , as indicated in fig7 , the distal ends 63 of the retractable electrode devices 62 are retained within the body mechanism 61 . once the body mechanism 61 is suitably placed inter - gyrally as desired , i . e ., in between two lateral walls of the brain , levers 66 can be operated by pairs of control leads or wires 67 to cause the distal ends 63 of the electrode devices 62 to the pushed into the brain tissue adjacent thereto . the levers 66 are mounted on an inner surface 68 of the body mechanism 61 . the control wires 67 can be operated manually , in which case pulling one of the pair of wires 67 extends the associated distal end 63 into the tissue and pulling the other one of the pair of wires 67 retracts the associated distal end 63 into the body mechanism 61 . it is to be understood that other precision control means , such as using stepper motors , dc motors or other suitable mechanisms may also be used for the purpose of extending and retracting the distal ends 63 into and from the adjacent brain tissue . if stepper motors are used , the control wires are attached to the stepper motor shaft so that rotating the motor in one direction ( for example , clockwise ) pushes the distal end into the brain tissue while rotating the motor in the opposite direction ( for example , counterclockwise ) retracts the distal end back into the shaft . it is to be understood that the stepper motors may be positioned outside the electrode structure . while any stepper motor can be used , use of one or more micro - stepper motors allows precise positioning of the distal ends 63 . for example , micro - stepper motors can be used to advance the distal ends 63 into the tissue in small steps for precise positioning thereof . either separate motors can be used to control each distal end 63 separately , or one motor can be used to simultaneously extend / retract some or all of the distal ends 63 as desired for a particular application . although only three electrode devices 62 are shown in fig7 , any number of the electrode devices 62 can be used to obtain as much spatial resolution as desired . the presence of several of the electrode devices 62 spaced around the body mechanism 61 provides three - dimensional information of the bea . the distal ends 63 of the electrode devices 62 are connected in communication with conductors 69 that can be used for recording the bea . it is to be understood that one or more contact surfaces 71 on an outer surface of the body mechanism 61 , as hereinbefore described , may be used in combination with the electrode devices 62 for a particular application as needed . a second modified embodiment 60 of the unitized electrode with three - dimensional capabilities for detection and control of brain state changes , designated by the numeral 75 , is shown in fig8 a and 8b , wherein channels 76 formed in a body mechanism 77 are utilized to slidably insert electrode wires 78 therethrough . the body mechanism 77 is constructed to insulate the electrode wires 78 from each other , such as by constructing the body mechanism 77 from insulating material , such as polyurethane or the like or lining the channels 76 with insulating material . an application of embodiment 75 can be described as follows : first the body mechanism 77 is inserted as desired into a fold of the gyrus . distal ends of the electrode wires 78 are slidably pushed through the channels 76 into the brain tissue as desired once the body mechanism 77 is in place . as hereinbefore described , it is to be understood that one or more contact surfaces 79 on an outer surface of the body mechanism 77 may be used in combination with the electrode wires 78 for a particular application as needed . a fragmentary and schematic illustration of a variation of the second modified embodiment 60 of the unitized electrode with three - dimensional capabilities for detection and control of brain state changes , designated by the numeral 85 , is shown in fig8 c , wherein a cannula 86 is slidably inserted through each channels 87 formed in body mechanism 88 and an electrode wire 89 is slidably inserted therethrough . an application of embodiment 85 can be described as follows : first the body mechanism 88 is inserted as desired into a fold of the gyrus . the cannula 86 is then pushed into the brain tissue as desired once the body mechanism 88 is in place . the cannula 86 is more rigid than the electrode wire 89 , thus enabling easier access and penetration into the brain tissue . after inserting the distal end of the cannula 86 a desired distance into the adjacent brain tissue , the more flexible ( less rigid ) electrode wire 89 is then guided and directed by the inserted cannula 86 as the electrode wire 89 is slidably extended through the cannula 86 , at least to the outer extremity of the distal end of the cannula 86 . without displacing the inserted electrode wire 89 , the cannula 86 is then retracted into the body mechanism 88 , thereby exposing the brain tissue to only the distal end of the electrode wire 89 . due to the elasticity of the brain tissue , the brain tissue closes around the distal end of the electrode wire 89 to form and maintain good communication contact therebetween after the cannula 86 is retracted . it is to be understood that the body mechanism 88 may contain several channels 87 , each having a cannula 86 and electrode wire 89 therein as described . also as hereinbefore described and illustrated , it is to be understood that one or more contact surfaces on an outer surface of the body mechanism 88 may be used in combination with the electrode wires 89 for a particular application as needed . fig8 c is an enlarged and schematic illustration of a first activating mechanism 90 , such as a stepper motor , being used to slidably displace the cannula 86 through the channel 87 and a second activating mechanism 91 being used , independently of the first activating mechanism 90 , to slidably displace the electrode wire 89 through the cannula 86 . a variation of the present invention is referred to herein as a “ hybrid ” as it consists of a macroelectrode having a diameter of approximately 1 . 1 – 2 mm with its own external recording surfaces , containing internally disposed mesoelectrodes having diameters of approximately 0 . 1 – 1 mm which can be deployed to increase dimensionality of recording from one - dimensional to up to three - dimensional . these hybrid electrodes are designed for detection and control of states of subcortical structures ( i . e , hippocampus ) offering great flexibility , wherein the mesoelectrodes will be deployed only if improved localization signal quality or control are needed . a third modified embodiment of the unitized electrode with three - dimensional capabilities for detection and control of brain state changes , designated by the numeral 92 is shown , in fig9 . the third modified embodiment 92 includes a plate portion 93 and a plurality of shaft portions 94 . as hereinbefore described , each shaft portion 94 may have a plurality of recording and / or stimulating electrode surfaces 95 separated by insulating material 96 , as indicated on only one of the shaft portions 94 for simplification of illustration . each of the recording and / or stimulating electrode surfaces 95 is independently connected to a different one of the conductors 97 . in addition , the lower surface 98 of the plate portion 93 may have a single recording and / or stimulating contact surface connected in communication with a separate one of the conductors 97 . application of the third modified embodiment is substantially similar to that indicated in fig6 c for electrode 50 . the multiple shaft portions 94 allow a further improved three - dimensional resolution of the bea . for some applications , it may be desirable that a plurality of the cannulae be slidably nested one within another to extend farther into the brain tissue . summarizing , those skilled in the art realize that : a ) the shape of the electrode component resting over the cortical surface 4 ( which in the preferred embodiment for a disk - type embodiment of the present invention ) may have any desired shape as appropriate for any particular application , such as rectangular , square , etc . moreover , the shape thereof may be tailored to conform to the top or exposed part of a gyrus over which it will be placed ; b ) the electrode may be constructed of materials with high thermal and electrical conductivity such as carbon nanotubes ; and c ) the shape , size and number of contact surfaces and number , diameter and lengths of the shafts may vary with the application for which it is being used . considerable improvements in temporo - spatial resolution , stability of target coverage and of signal acquisition , higher signal / noise ratio of brain signals , and multi - site recording and control capabilities at two or more spatial scales are provided by the present invention comprising a unitized electrode . through simple changes in design and variations in its length , the device of the present invention can be used for recording of : ( i ) intra - cortical activity only ; ( ii ) activity from exposed or non - exposed cortical surfaces only ; ( iii ) simultaneous recording of intracortical and epicortical ( surfaces ) activities from the same or different regions ; ( iv ) inter - gyral activity from non - exposed cortical walls only ; ( v ) inter - gyral and intracortical activities simultaneously ; ( vi ) trans - hemispheric activity from cortical surfaces , intra - cortical regions , white matter and sub - cortical hemispheric structures / nuclei , such as the thalamus , increasing its anatomo - functional range for detection and control of state changes . the multi - site and multi - modal ( electrical , thermal , chemical optical or other classes of signals ) recording and control capabilities / functions can be applied congruously wherein recording and control are performed through the same device or portion thereof , or incongruously wherein recording and control are carried out either through different portions of the same device or through different devices . furthermore , such unitized functions can be performed either synchronously in time , or asynchronously in time . also , detection of brain state changes may be accomplished using electrical or chemical signals and control may be exerted by , for example , cooling the region of interest . since the reciprocal projections between the cortex and deep nuclei , such as the thalamus , follow a radial pattern , the device of the present invention allows recording and control of signal / brain states along different levels of the same region / domain in a simultaneous or sequential fashion . application of additional devices allows similar degrees of flexibility and multiplicity of functions over different regions . the invention disclosed herein is more efficient and causes less trauma than prior art by requiring fewer electrodes and tissue penetrations and smaller holes , than the previously - required burr holes , for implantation . it is also more cost - effective in that it requires shorter surgical time compared to prior art approaches . the present invention may also be used for detection purposes as taught in u . s . pat . no . 5 , 995 , 868 issued nov . 30 , 1999 to ivan osorio et al . to summarize , by using the invention disclosed herein , recording / sensing or control of state changes can be performed integrally ( across all regions / domains sampled by one or more devices ) or differentially ( selected regions / domains sampled by one or more devices ). it is to be understood that while certain forms of the present invention have been illustrated and described herein , it is not to be limited to the specific forms or arrangement of parts described and shown .
an electrode with three - dimensional capabilities for detection and control of brain state changes of a subject . the electrode includes a disk portion having an upper surface and a lower surface , and a shaft portion secured to and extending perpendicularly outwardly from the lower surface of the disk portion ; the shaft portion having an outer surface . the disk portion and shaft portion may include one or more recording or stimulating contact surfaces structured to operatively interact with the brain of a subject . insulating material isolates each of the recording or stimulating contact surfaces from each other . at least one conductor operatively and separately connect each of the recording or stimulating contact surfaces in communication with external apparatus . the disk portion and shaft portion are structured relative to each other to operatively provide support and anchoring for each other while providing three - dimensional capabilities for detection and control of brain state changes of a subject . modified embodiments include insertible / retractable electrode wires , both contained in channels and sheathed in axially displaceable cannulae ; activating mechanisms for inserting / retracting the electrode wires and / or cannulae ; and multiple shaft portions .