Abstract:
An electrical stimulator line protector, comprising a case having an upper surface and a lower surface, the case configured for implantation in the scalp or other subcutaneous areas of a patient; a storage slot disposed between the upper surface and the lower surface of the case, the slot configured to allow at least one electrical line to coil therearound, the upper surface, the lower surface and the slot to thereby shield the line.

Description:
This Application is a Continuation-in-Part of application Ser. Nos. 12/790,841, 12/790,842 and Ser. No. 12/790,843, all filed on May 30, 2010, application Ser. No. 12/790,841 is a Continuation of application Ser. No. 11/255,259, filed on Oct. 21, 2005; application Ser. No. 12/790,842 is a division of application Ser. No. 11/255,259, filed on Oct. 21, 2005; application Ser. No. 12/790,843 is a division of application Ser. No. 11/255,259, filed on Oct. 21, 2005. Application Ser. No. 11/255,259 is presently patented as U.S. Pat. No. 7,729,780. Application Ser. No. 11/255,259 claimed the benefit of U.S. provisional patent application 60/620,905, filed Oct. 21, 2004, all of which are incorporated by reference as if set forth fully herein. 
     RELATED APPLICATION 
     This application claims priority from U.S. Provisional Patent Application, Ser. No. 60/620,905, filed Oct. 21, 2004 and entitled Various Apparatus and Methods for Deep Brain Stimulating Electrodes and also to U.S. Utility patent application Ser. No. 11/255,259, filed Oct. 21, 2005, which issued as U.S. Pat. No. 7,729,780, on Jun. 1, 2010 and also to U.S. Utility patent application Ser. Nos. 12/790,841, 12/790,842 and 12/790,843, all filed on May 30, 2010 and also entitled Various Apparatus and Methods for Deep Brain Stimulating Electrodes, all of which are incorporated by reference as if set forth fully herein. 
    
    
     TECHNICAL FIELD OF THE INVENTION 
     The technical field of the invention relates to deep brain stimulating probes, such as electrodes. 
     The technical field of the invention relates to delivering infusates, with medicinal properties, into the brain. 
     The present invention relates to a multi-directional synchronous deploying deep brain stimulating electrodes. 
     The technical field of the invention relates to a multi-directional selectively deployable deep brain stimulating electrodes. 
     The present invention relates to a large diameter deep brain stimulating electrodes. 
     The present invention relates to a curved guide for anatomic arc placement of deep brain stimulating electrode. 
     The present invention relates to apparatus for delivering infusates, with medicinal properties, into the brain. 
     The present invention relates to a depth graduated deep brain-stimulating electrode. 
     The present invention relates to apparatus for labeling, designating target site, uniquely identifying the electrode and/or determining right/left laterality of subcutaneously implanted electrodes, pulse generator connectors (including those with extension kits) or any or all elements of the implanted system. 
     The present invention relates to subdermal electrode shields. 
     BACKGROUND OF THE INVENTION 
     A variety of disabling diseases affecting the central nervous system have proven responsive to treatment using electrical stimulation of specific anatomic targets within the human brain. Examples of disabling diseases affecting the central nervous system are Parkinson&#39;s disease, multiple sclerosis and the like. 
     At the present time, devices designed to produce deep brain stimulation use a standard set of components including a pulse generator and an electrode. The pulse generator is electrically connected to the electrode and the electrode is surgically implanted within a patient&#39;s brain. The pulse generator can produce a modulatable electrical field/current. At the present time, the electrode elements have four electrode contacts arranged as narrowly spaced bands on the terminal end of a stimulating electrode. 
     The physiologic effect of electrical stimulation can be modulated by altering the amplitude, frequency or pulse width of the electrical current, emitted from the electrode deeply implanted within the patient&#39;s brain. 
     Because the current deep brain stimulating probes have four electrodes, it is currently possible to achieve a certain limited degree of flexibility in the electrical “footprint” generated by the electrode by changing which electrode is operating, and the other parameters discussed above. 
     If the initial surgical placement of the electrode in the brain is sufficiently “off-target,” it is impossible to capture the target within the available “footprint” of the electrical field generated by the electrodes of the currently available deep brain stimulating devices. 
     SUMMARY OF THE INVENTION 
     The present invention provides for multi-directional synchronous deploying deep brain stimulating electrodes. 
     The invention provides for multi-directional selectively deployable deep brain stimulating electrodes 
     The present invention provides for large diameter deep brain stimulating electrodes. 
     The present invention provides for a curved electrode, curved stylet and/or curved guide for anatomic arc placement of a deep brain stimulating electrode. 
     The present invention provides for apparatus for delivering infusates, with medicinal properties, into the brain. 
     The present invention provides for depth graduated deep brain-stimulating electrode. 
     The present invention provides for apparatus for labeling designation target site, uniquely identifying the electrode and/or determining right/left laterality of subcutaneously implanted pulse generator connectors (including those with extension kits) or any other or all elements of the implanted system. 
     The present invention provides for subdermal electrode shields. 
     These and other embodiments will be more fully appreciated from the description below. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  is perspective view of the current state of the technology, i.e. prior art. The X illustrates the location of the area requiring electrical stimulation in the patient&#39;s brain. As noted above, four electrodes are arranged as narrowly spaced bands on the terminal end of the probe.  FIGS. 1 ,  1 A,  1 B,  1 C and  1 D illustrate use of a current deep brain stimulating probe where the surgeon&#39;s initial placement of the probe allows the electrical “footprint” of the electrodes to accurately deliver electrical stimulation to a specific anatomic target within the human brain. 
         FIG. 1A  is a detailed view of the four electrodes seen in  FIG. 1 . 
         FIG. 1B  is a detailed view of the four electrodes seen in  FIG. 1 . 
         FIG. 1C  is a detailed view of the four electrodes seen in  FIG. 1 . 
         FIG. 1D  is a detailed view of the four electrodes seen in  FIG. 1 . 
         FIG. 2  is perspective view of the current state of the technology, i.e. prior art. The “X” illustrates the location of the area requiring electrical stimulation in the patient&#39;s brain. As noted above, four electrodes are arranged as narrowly spaced bands on the terminal end of the probe.  FIGS. 2 ,  2 A,  2 B,  2 C and  12 D illustrate use of a current deep brain stimulating probe where the surgeon&#39;s initial placement of the probe is sufficiently off-target that the electrical “footprint” of the electrodes cannot stimulate the area of the patient&#39;s brain requiring electrical stimulation. In other words, the surgeon has missed the target in the patient&#39;s brain and must withdraw the probe and reinsert the probe into the patient&#39;s brain. This is highly undesirable because it requires the surgeon to make an extra hole in the patient&#39;s brain and further traumatizes the patient&#39;s brain tissue. 
         FIG. 2A  is a detailed view of the four electrodes seen in  FIG. 2  with a first electrode energized. 
         FIG. 2B  is a detailed view of the four electrodes seen in  FIG. 2  with a second electrode energized. 
         FIG. 2C  is a detailed view of the four electrodes seen in  FIG. 2  with a third electrode energized. 
         FIG. 2D  is a detailed view of the four electrodes seen in  FIG. 2  with a fourth electrode energized. 
         FIG. 3  is a perspective view of the multi-directional synchronous deploying deep brain stimulating electrodes of the present invention. 
         FIG. 3A  is a detailed perspective view of the present invention seen in  FIG. 3  with the electrodes undeployed. 
         FIG. 3B  is a detailed perspective view of the present invention seen in  FIGS. 3 and 3A  with the electrodes deployed. 
         FIG. 3C  is a detailed perspective view of the present invention seen in  FIGS. 3 and 3A  with a first electrode energized. 
         FIG. 3D  is a detailed perspective view of the present invention seen in  FIGS. 3 and 3A  with a second electrode energized. 
         FIG. 3F  is a detailed perspective view of the present invention seen in  FIGS. 3 and 3A  with a third electrode energized. 
         FIG. 3G  is a detailed perspective view of the present invention seen in  FIGS. 3 and 3A  with a fourth electrode energized. 
         FIG. 3H  is a detailed perspective view of the present invention seen in  FIGS. 3 and 3A  with a fifth electrode energized. 
         FIG. 4  is a perspective view of the multi-directional selectively deployable deep brain stimulation electrodes of the present invention with the patient&#39;s scalp opened to expose the underlying tissue. 
         FIG. 4A  is a perspective view of the multi-directional selectively deployable deep brain stimulating electrodes of the present invention in use with the patient&#39;s scalp replaced. This embodiment allows use of the device outside of an operating room environment. 
         FIG. 4B  is a detailed perspective view of the present invention of the present invention seen in  FIGS. 4A and 4B  with a first electrode deployed and energized. 
         FIG. 5  is a perspective view of the multi-directional selective deployable deep brain stimulation electrodes of the present invention with an electrode energized. 
         FIG. 5A  is a detailed perspective view of the energized electrode seen in  FIG. 5 . 
         FIG. 6  is a perspective view of the multi-directional selective deployable deep brain stimulation electrodes of the present invention with an electrode energized. 
         FIG. 6A  is a detailed perspective view of the deployed and energized electrode seen in  FIG. 6 . 
         FIG. 7  is a perspective view of the large diameter deep brain stimulation electrode of the present invention. 
         FIG. 7A  is a detailed perspective view of the large diameter deep brain stimulation electrode of the present invention with a first electrode energized. 
         FIG. 7B  is a detailed perspective view of the large diameter deep brain stimulation electrode of the present invention with a second electrode energized. 
         FIG. 7C  is a detailed perspective view of an alternative embodiment of the large diameter deep brain stimulation electrode of the present invention. 
         FIG. 8A  is a perspective view of the curved guide for anatomic arc placement of a deep brain stimulation electrode of the present invention. 
         FIG. 8B  is curved guide for anatomic arc placement of a deep brain stimulation electrode shaped so as to avoid the cingulate gyrus of the human brain. 
         FIG. 8C  is a curved guide for anatomic arc placement of a deep brain stimulation electrode shaped so as to avoid the mesial temporal lobe structures of the human brain. 
         FIG. 9  shows an embodiment of an infusate delivering apparatus of the present invention implanted within a patient&#39;s brain. 
         FIG. 9A  is an alternative embodiment of an infusate delivering apparatus of the present invention. 
         FIG. 9B  is an alternative embodiment of the tendrils of the present invention using interior passages to deliver infusate along the tendrils of the infusate delivering apparatus of the present invention. 
         FIG. 9C  is an alternative embodiment of the tendrils of the present invention using weep holes to deliver infusate along the tendrils of the infusate delivering apparatus of the present invention. 
         FIG. 9D  is an alternative embodiment of the tendrils of the present invention using a gutter to deliver infusate along the tendrils of the infusate delivering apparatus of the present invention. 
         FIG. 10  is an alternative embodiment of an infusate delivering apparatus of the present invention. 
         FIG. 11  is a perspective view of a depth graduated deep brain stimulation electrode of the present invention. 
         FIG. 11A  is a detailed perspective view of the depth graduated deep brain stimulation electrode and left/right connector designators of the present invention. 
         FIG. 11B  is a perspective view of a surgically implanted neurostimulator, also known as a “pulse generator”, with deep brain stimulation electrodes implanted in a patient&#39;s brain using the depth graduated deep brain stimulation electrode of the present invention. 
         FIG. 12  is a perspective view of a subdermal electrode shield of the present invention implanted beneath a patient&#39;s scalp. 
         FIG. 12A  is a perspective view of an alternative embodiment of a subdermal electrode shield. 
         FIG. 12B  is a perspective view of a second alternative embodiment of a subdermal electrode shield. 
         FIG. 12C  is a perspective view of another alternative embodiment of a subdermal electrode shield. 
         FIG. 12D  is a perspective view of another alternative embodiment of a subdermal electrode shield. 
         FIG. 12E  is a cross-sectional view of the electrode shield shown in  FIG. 12C . 
         FIG. 12F  is a perspective view of another alternative embodiment of a subdermal electrode shield. 
         FIG. 12G  is a perspective view of another alternative embodiment of a subdermal electrode shield. 
         FIG. 12H  is a perspective view of another alternative embodiment of a subdermal electrode shield. 
         FIG. 12I  is a perspective view of an alternative embodiment of a subdermal electrode shield. 
         FIG. 12J  is a cross sectional view of the electrode shield shown in  FIG. 12I . 
         FIG. 12K  is a perspective view of an alternative embodiment of a subdermal electrode shield. 
         FIG. 12L  is a perspective view of an alternative embodiment of a subdermal electrode shield. 
         FIG. 12M  is a perspective view of an alternative embodiment of a subdermal electrode shield. 
         FIG. 12N  is a perspective view of an alternative embodiment of a subdermal electrode shield. 
         FIG. 12O  is a perspective view of an alternative embodiment of a subdermal electrode shield. 
         FIG. 12P  is a detailed view of an alternative embodiment of a subdermal electrode shield further including a gasket. 
     
    
    
     DESCRIPTION OF THE PREFERRED EMBODIMENTS 
     Corresponding reference numbers indicate corresponding parts throughout the several views of the drawings and specification. 
     It should also be noted that the terms “subdermal electrode shield,” for purposes of this application be considered the same as an “electrical stimulator line protector.” 
     A variety of disabling diseases affecting the central nervous system have proven responsive to treatment using electrical stimulation of specific anatomic targets T. As such, it is desirable for the electrical field E of stimulating probe P, seen as a shaded area E and also known as an electrical “footprint,” to reach the targeted portion T of the human brain, as seen in  FIG. 1B . 
       FIG. 1  illustrates a currently available deep brain stimulation electrode probe P with four electrodes (A, B, C and D) arranged as narrowly spaced bands on the terminal end of a stimulating probe P. The physiologic effect of the stimulation of probe P can be modulated by altering which electrode (A, B, C or D) is energized or by altering the amplitude, frequency or pulse width of the electrical current. However, the four-banded electrodes seen in  FIG. 1  are in fixed in position on stimulating probe P.  FIG. 1  also shows target T. Target T is depicted by an “X” throughout the present application. 
       FIG. 1A  shows a first electrode A of probe P as it is energized. As can be seen in  FIG. 1A , electrical field E does not coincide with Target T and the electrical stimulation provided by electrode A is of limited or no treatment value. 
       FIG. 1B  shows a second electrode B of probe P as it is energized. As can be seen in  FIG. 1B , electrical field E coincides with Target T and the electrical stimulation provided by electrode B likely provides therapeutic value to the patient. 
       FIG. 1C  shows a third electrode C of probe P as it is energized. As can been seen in  FIG. 1C , electrical field E does not coincide with Target T and the electrical stimulation provided by electrode C is of limited or no treatment value. 
       FIG. 1D  shows a fourth electrode D of probe P as it is energized. As can been seen in  FIG. 1D , electrical field E does not coincide with Target T and the electrical stimulation provided by electrode D is of limited or no treatment value. 
       FIG. 2  illustrates a potential situation where a surgeon&#39;s initial surgical placement of probe P is sufficiently off target such that it may be impossible to capture target T with the available electrical field E. In this situation, the surgeon may have to withdraw probe P and reinsert it into the patient&#39;s brain. This is considered undesirable because the surgeon will have to make a second hole through the patient&#39;s brain. 
       FIG. 2A  shows a first electrode A of probe P as it is energized. As can be seen in  FIG. 2A , electrical field E does not coincide with Target T and the electrical stimulation provided by electrode A is of limited or no treatment value. 
     Unlike  FIG. 1B ,  FIG. 2B  shows a second electrode B of probe P as it is energized. As can be seen in  FIG. 2B , electrical field E does not coincide with Target T and the electrical stimulation provided by electrode B is of limited or no treatment value. 
       FIG. 2C  shows a third electrode C of probe P as it is energized. As can been seen in  FIG. 2C , electrical field E does not coincide with Target T and the electrical stimulation provided by electrode C is of limited or no treatment value. 
       FIG. 2D  shows a fourth electrode D of probe P as it is energized. As can been seen in  FIG. 2D , electrical field E does not coincide with Target T and the electrical stimulation provided by electrode D is of limited or no treatment value. 
       FIG. 3  shows a perspective view of a multi-directional synchronous deploying deep brain stimulation probe  100  implanted within a human brain. Probe  100  includes shaft  102 , sleeve  104 , openings  106 , stiffener  108  and tendrils  110 . Probe  100  is placed using standard techniques such as frame based, frameless or image guided placement techniques.  FIG. 3  shows probe  100  positioned within the human brain. 
       FIGS. 3A and 3B  show stiffener  108 . A surgeon may elect to use stiffener  108  if he desires a more rigid probe  100 . A surgeon electing to use a less rigid probe  100 , would use elect to remove stiffener  108 . 
       FIG. 3A  shows sleeve  104  repositioned such that multiple tendrils  110  advance in a gentle trajectory into the surrounding brain tissue through openings  106 , as seen in  FIG. 3B .  FIG. 3B  also shows electrodes  112 . 
       FIG. 3  shows line  114  and connector  116 . Line  114  interconnects electrodes  112  to pulse generator G. Pulse generators G are well known in the prior art. 
     FIGS.  3  and  3 C- 3 H show probe  100  in use. Specifically,  FIG. 3C  shows probe  100  with a first tendril  110  extended and electrode  112  energized. The electrical field E generated by electrode  112  is shown as the shaded area throughout the figures in the present patent application. As seen in  FIG. 3C , electrical field E does not coincide with target T. As such, the electrical stimulation provided by electrode  112  is of limited or no treatment value. 
       FIG. 3D  shows a probe  100  with a second tendril  110  extended and electrode  112  energized. Because the electrical field E does not coincide with target T, the electrical stimulation provided by electrode  112  is of limited or no treatment value. 
       FIG. 3E  shows a probe  100  with a third tendril  110  extended and electrode  112  energized. Because the electrical field E does not coincide with target T, the electrical stimulation provided by electrode  112  is of limited or no treatment value. 
       FIG. 3E  shows a probe  100  with a fourth tendril  110  extended and electrode  112  energized. Because the electrical field E does not coincide with target T, the electrical stimulation provided by electrode  112  is of limited or no treatment value. 
       FIG. 3F  shows a probe  100  with a fifth tendril  110  extended and electrode  112  energized. Because the electrical field E does not coincide with target T, the electrical stimulation provided by electrode  112  is of limited or no treatment value. 
       FIG. 3G  shows a probe  100  with a sixth tendril  110  extended and electrode  112  energized. Because the electrical field E coincides with target T, the electrical stimulation provided by electrode  112  likely provides therapeutic value to the patient. 
       FIG. 3H  shows a probe  100  with a seventh tendril  110  extended and electrode  112  energized. Because the electrical field E does not coincide with target T, the electrical stimulation provided by electrode  112  is of limited or no treatment value. 
     It is also within the scope of the present invention to include a brainwave reader  118  [seen in  FIG. 3H ]. Preferably, brain wave reader  118  would be sufficiently small that it could fit on tendrils  110  of probe  100 . It is also within the scope of the present invention that multiple probes  100  could be implanted within a patient&#39;s brain with each tendril  110  including a brain wave reader  118  or brain wave readers  118  on only selected tendrils  110 . Use of a brain wave reader  118  could allow a closed-loop system where selected electrodes  112  are energized in response to undesirable patterns of neural activity. 
     If one or more probes  100 , or any other type of probe shown or described in the present application or its equivalent, were implanted within a patient&#39;s brain, an external brain wave reader [not shown] could use the information generated by the brain wave monitors  118  to record neural activity and to “map” neural activity. In other words, probe  100  could monitor neural activity and also deliver electrical stimulation in response to detected patterns of neural activity in a patient. For example, the early stages of an epileptic seizure generate a recognizable pattern of neural activity in the human brain. One or more brain wave monitors  118  could detect the pattern of neural activity and energize one or more electrodes  112  on one or more probes  100  in order to counteract the undesirable neural activity patterns. It is within the scope of the present invention that undesirable neural activity such as found with seizures, depression or tremors or the like, could be counter-acted by using brain wave monitors  118  to detect the undesirable patterns and energizing the appropriate sequence of electrodes  112  to reduce or eliminate such undesirable neural activity patterns. As discussed later in this application, infusates might also be delivered into the patient&#39;s brain to counter-act undesirable patterns of brain wave activity. This infusion of infusates could be in conjunction with energizing the appropriate sequence of electrodes  112  to reduce or eliminate such undesirable neural activity patterns. 
     Similarly, a partially or fully paralyzed person, because of a damaged or severed spinal column, might have one or more probes  100  implanted in their brain. As discussed above, each probe  100  would include an electrode  112  and a brain wave monitor  118 . The brain wave monitors  118  would “map” the paralyzed person&#39;s brain wave patterns when the patient was thinking about performing a particular body function. For example, if a paralyzed person were instructed to think about moving their left foot forward, the brain wave monitors  118  would record this pattern of neural activity. Obviously, the patient&#39;s left foot would not move because the patient is paralyzed and there is either a damaged or severed electrical connection between the patient&#39;s brain and the nerves and muscles of the patient&#39;s left foot. However, the pattern of neural activity associated with moving the patient&#39;s left foot forward would be stored within an external brain wave reader [not shown]. It is well known which groups of muscles move a human&#39;s left foot forward. Once the neural pattern for moving the left foot is recorded by the external brain wave reader [not shown], each time this pattern of neural activity is detected in the patient&#39;s brain, electrodes implanted in the patient&#39;s body could be energized to stimulate the patient&#39;s muscles to move the patient&#39;s left foot forward. In this way, the external brain wave reader [not shown] would “learn” to mimic the range of motion for a paralyzed patient and thereby replace the severed or damaged spinal cord. Obviously, the present invention is not limited to forward motion of the left foot. In fact, it is considered that it is within the scope of the present invention that a patient could relearn how to control the areas of his body that are not in communication with his or her brain because of a severed or damaged spinal cord. 
     It is contemplated that any type of deep brain stimulation probe that is disclosed by this application could accomplish the goal of restoring motion to a paralyzed person and this disclosure is not limited to a multi-directional synchronous deploying deep brain stimulation probe  100 . 
       FIG. 4  shows multi-directional selectively deployable deep brain stimulation probe  200  implanted within a human brain. Probe  200  includes shaft  202 , reservoir  204 , openings  206 , stiffener  208  and tendrils  210 . Probe  200  is placed using standard techniques such as frame based, frameless or image guided placement techniques. 
       FIG. 4  shows probe  200  positioned within the human brain. FIGS.  4 A and  4 BB show a stiffener  208 . A surgeon may elect to use stiffener  208  if he desires a more rigid probe  200 . A surgeon electing to use a less rigid probe  200 , would elect to remove stiffener  208 . 
       FIGS. 4 ,  4 A and  4 B show reservoirs  204  in communication with tendrils  210 . It is within the scope of the invention that reservoirs  204  could selectively urge tendrils  210  advance in a gentle trajectory into the surrounding brain tissue through openings  206 , as seen in  FIG. 4B . Specifically, reservoirs  204  could be hydraulic reservoirs, mechanical or electrical devices, or other similar mechanism that would urge one or more tendrils  210  to advance out of openings  206 . Hydraulic reservoirs  204  are shown by way of example. However, other means of urging tendrils  210  outward are within the scope of the present invention.  FIG. 4B  also shows electrodes  212 . Electrodes  212  are preferably at the ends of tendrils  210 . 
       FIG. 4  shows line  214  and connector  216 . Line  214  interconnects electrodes  212  to pulse generator G. Pulse generators G are well known in the prior art. 
       FIGS. 4 and 4B  shows a syringe injecting hydraulic fluid into one of the cavities of reservoir  204 . When hydraulic fluid is urged into the cavity seen in  FIG. 4 , tendril  210 , seen in  FIG. 4B , is urged out from opening  206  and tendril  210  advances in a gentle trajectory into the surrounding brain tissue. After tendril  210  extends into the surrounding brain tissue, electrode  212  is energized and creates electrical field E. In the example shown in  FIG. 4B , target T and electrical field E do not coincide and the electrical stimulation provided by electrode  212  is of limited or no treatment value. 
       FIG. 4A  shows multi-directional selectively deployable deep brain stimulation probe  200  with scalp S replaced. Using probe  200  with scalp S replaced is vitally important for operation of probe  200  outside of an operating room environment. Because probe  200  can operate with scalp S replaced, injector I must pass through scalp S in order to access reservoirs  204 . As discussed above, when tendril  210  extended outward and electrode  212  energized, either with scalp S pulled back ( FIG. 4 ) or replaced ( FIG. 4A ), electrical field E did not coincide with target T and the electrical stimulation provided by electrode  212  is of limited or no treatment value. As such, a surgeon will select an alternative cavity of reservoir  204  in order to urge a second tendril  210  outward. 
       FIGS. 5 and 5A  show a surgeon selecting an alternative cavity of reservoir  204  in order to urge a second tendril  210  outward. As seen in  FIG. 5A , the surgeon has chosen the correct cavity of reservoir  204  and tendril  210  is urged outward through openings  206 . When electrode  212  is energized, electrical field E coincides with target T and the electrical stimulation provided by electrode  112  likely provides therapeutic value to the patient. 
       FIGS. 6 and 6A  show a surgeon selecting a third cavity in reservoir  204  and illustrates how tendril  210  is selectively urged outward through opening  206 . Because target T has already been electrically stimulated,  FIGS. 6 and 6A  are included to emphasize that tendrils  210  of probe  200  are selectively deployable. 
       FIGS. 7 ,  7 A and  7 B show a perspective view of a large diameter deep brain stimulation probe  300  implanted within a human brain. Probe  300  includes shaft  302 , placodes  306  and stiffener  308 . Probe  300  is placed using standard techniques such as frame based, frameless or image guided placement techniques. 
       FIG. 7  shows probe  300  positioned within the human brain.  FIG. 7A  shows stiffener  308 . A surgeon may elect to use stiffener  308  if he desires a more rigid probe  300 . A surgeon electing to use a less rigid probe  300 , would use elect to remove stiffener  308 . 
       FIG. 7A  shows placode  306  positioned on probe  300 . In one embodiment, small multiple placodes  306  are radially oriented and staggered along the length of shaft  302 . When each placode  306  is energized, placode  306  generates an electrical field E, such as seen in  FIG. 7A . As seen in  FIG. 7A , when first placode  306  is energized, electrical field E did not coincide with target T and the electrical stimulation provided by placode  306  is of limited or no treatment value. As such, a surgeon will select an alternative placode  306  to energize. 
       FIG. 7B  shows when a second placode  306  is energized by a surgeon. Second placode  306  creates and electrical field E. When second placode  306  is energized, electrical field E coincides with target T and the electrical stimulation provided by placode  306  likely provides therapeutic value to the patient. 
       FIG. 7C  shows an alternative embodiment of probe  300 . In the alternative embodiment of probe  300  seen in  FIG. 7C , placodes  306  are placed “single-file” along the longitudinal axis of probe  300  so that a simple rotation of probe  300  will allow modulation of the direction of electrical field E. 
       FIG. 7  also shows line  314  and connector  316 . Line  314  interconnects placodes  306  to pulse generator G. Pulse generators G are well known in the prior art. 
       FIG. 8A  is a perspective view of the curved guide for anatomic arc placement of a deep brain stimulation electrode  400  of the present invention. Probe  400  includes catheter  402 , groove  404 , orientation guide rail  406 , electrodes  412 , line  414  and connector  416 . Probe  400  is desirable because it is undesirable for a probe to pass through certain structures in the human brain. As such, probe  400  can be pre-curved to a shape to avoid certain neural structures in the human brain. Groove  404  and orientation guide rail  406  cooperatively guide shaft  408 . As seen in  FIG. 8C , electrodes  412  are disposed at regular intervals along shaft  408 . 
       FIG. 8B  shows probe  400  curved guide for anatomic arc placement of a deep brain stimulation electrode shaped so as to avoid the cingulate gyrus of the human brain. 
       FIG. 8C  is a curved guide for anatomic arc placement of a deep brain stimulation electrode  400  shaped so as to avoid the mesial temporal lobe structures of the human brain. It is within the scope of the present invention that probe  400  could be pre-curved to more readily allow a surgeon to avoid structures within in the human brain. 
     It is well known that infused drugs or chemicals are more efficacious if delivered directly to desired locations of the human brain, rather than delivered indirectly through an intravenous drip and carried through the patient&#39;s blood stream.  FIG. 9  shows infusate probe  500  positioned in a brain to deliver infusates to targeted portions of the patient&#39;s brain. It is within the scope of the present invention that infusate probe  500  could be used with the scalp S replaced. When scalp S is replaced, infusate could be withdrawn from a reservoir located either outside or inside the patient&#39;s body. When a patient uses an interior reservoir, infusate probe  500  could be used outside an operating room environment. 
       FIGS. 9 and 9A  shows an infusate delivery probe  500 . Infusate delivery probe  500  includes shaft  502 , openings  506 , stiffener  508 , tendrils  510 , radio frequency positioners  512  and lumens  518 . Shaft  502  may employ stiffener  508 . A surgeon may elect to use stiffener  508  if he desires a more rigid infusate delivery probe  500 . A surgeon electing to use a less rigid probe  500 , would use elect to remove stiffener  508 . Tendrils  510  could be selectively urged outward through openings  506 . It is desirable to obtain accurate information about the position of the terminal ends of tendrils  510 , using RTF positioners  512  because infusate  520  can be more accurately delivered to a desired location in the human brain if the position of tendrils  510  is accurately known. Probe  500  is placed using standard techniques such as frame based, frameless or image guided placement techniques. In addition, RTF positioners  512  allow a surgeon to identify the precise location of each tendril  510 . This allows a surgeon to selectively deploy a tendril  510  and deliver infusate to a targeted portion of the brain. In the embodiment of probe  500  seen in  FIGS. 9 and 9A , it is preferable for infusate  520  to be delivered through the terminal ends of tendrils  510 . 
       FIG. 9C  shows an alternative embodiment of tendril  510  where infusate  520  is delivered through weepholes  509  located along tendril  510 . This alternative embodiment may also use RTF positioners  512  to allow a surgeon to identify the precise location of each tendril  510 . 
       FIG. 9D  shows an alternative embodiment of tendril  510  where infusate is delivered through a gutter  511  disposed longitudinally along tendril  510 . This alternative embodiment may also use RTF positioners  512  to allow a surgeon to identify the precise location of each tendril  510 . 
       FIG. 10  shows an alternative infusate delivery probe  600 . Probe  600  includes shaft  602 , openings  606 , stiffener  608 , electrodes  612  and lumens  618 . Shaft  602  may employ stiffener  608 . A surgeon may elect to use stiffener  608  if he desires a more rigid infusate delivery probe  600 . A surgeon electing to use a less rigid probe  600 , would use elect to remove stiffener  608 . Infusate  620  flows out from a reservoir either external to the patient or surgically implanted within the patient and passes into the brain through lumens  618 . Electrodes  612  allow electrical stimulation a patient&#39;s brain while also delivering infusate  620 , as appropriate. 
       FIG. 11  shows a depth graduated deep brain stimulation probe  700 . Currently, deep brain stimulating probes P do not allow a surgeon to determine the depth that the probe P is inserted into the patient&#39;s brain. Indeed, as seen in  FIG. 1 , unless the surgeon has access to real time fluoroscopic imaging to monitor probe P&#39;s position, there are few if any means to allow a surgeon to precisely maintain the depth of probe P and precisely determine the position of electrodes A, B, C or D. If a surgeon knows the depth that he needs to insert probe P, or any alternative embodiment discussed in the present application, the surgeon could determine which color band  710  corresponded to the appropriate depth and insert probe  700  into the patient&#39;s brain only until the color band for this depth is just visible above the insertion point into the patient&#39;s brain. 
       FIGS. 11 and 11B  show that at the present time, lines  114  are not laterally distinguishable. In other words, a surgeon may be uncertain which line  114  is connected to the left and right connections of pulse generator G, seen in  FIG. 11B , because lines  114  are implanted under the patient&#39;s skin. Therefore, it is desirable to label each line  114  as “left” or “right” along the entire length of the line  114 . Alternatively, it may be desirable to chose alternative colors for left line  114  and right line  114 . Conventionally, green is chosen for left and red for right. However, any system could work if different colors or markings were selected to distinguish lines  114 . Additional information encoded onto the electrode might include the anatomic target site of the electrode or any other data that might be useful. The information on the electrodes could be depicted in any form of colors, symbols, letters, radio opaque markers that could be visualized by x-ray, or even small RF tags that could be interrogated by an RF reader device. 
       FIG. 12  shows subdermal electrode shield  800 . Subdermal electrode shield includes case  802  and storage slot  804 . In the embodiment seen in  FIG. 12 , lines  114  are coiled around case  802  and inside storage slot  804 . When a surgeon is implanting probe P, the surgeon will be able to coil additional length of electrode inside storage slot  804 . In this way, a surgeon can also more readily avoid confusion over left and right lines  114  and protect the electrode leads from inadvertent injury when being externalized later or kinked or damaged through rough handling while trying to jam the electrodes under the skin in a haphazard fashion as they attempt to spring out of the subcutaneous pocket. It should be noted that in its preferred embodiment, subdermal electrode shield  800  is implanted under a patient&#39;s scalp or any subcutaneous area. Other embodiments of this device could include the capacity to simply uncoil a small amount of the electrode so that it could be attached to the rest of the mechanism without having to uncoil the entire length of the electrode from the protective device. 
       FIG. 12A  shows subdermal electrode shield  800 ′. Subdermal electrode shield includes casing  802 ′, internal coiled spring  803 ′ [not show], plug  805 ′ and mouth  807 ′. Lines  114  pass through mouth  807 ′ before connecting to probes P. Plug  805 ′ electrically interconnect lines  114  to pulse generator G. Because subdermal electrode shield  800 ′ is spring loaded, excess line  114  is withdrawn inside casing  802 ′ and excess line  114  is not exposed. A surgeon could “crimp” mouth  807 ′ to prevent line  114  being withdrawn inside casing  802 ′. It should be noted that in its preferred embodiment, subdermal spring loaded electrode shield  800 ′ s  is implanted under a patient&#39;s scalp or any other desired subcutaneous area. Other embodiments of this device could include the capacity to simply uncoil a small amount of the electrode so that it could be attached to the rest of the mechanism without having to uncoil the entire length of the electrode from the protective device. 
       FIG. 12B  shows subdermal electrode shield  800 ″. Subdermal electrode shield  800 ″ includes a casing  802 ″ and a mouth  807 ″. When a surgeon has completed implanting a probe P, the surgeon will be able to store any additional length of lines  114  inside shield  800 ″. In this way, a surgeon can also more readily avoid confusion over left and right lines  114  and can protect the electrode leads from inadvertent injury when being externalized later or being kinked or damaged from rough handling while attempting to jam the electrodes under the skin in a haphazard fashion as they out of the subcutaneous pocket. It should be noted that in its preferred embodiment, subdermal electrode shield  800 ″ is implanted under a patient&#39;s scalp or any subcutaneous area. Other embodiments of this device could include the capacity to simply uncoil a small amount of the electrode so that it could be attached to the rest of the mechanism without having to uncoil the entire length of the electrode from the protective device. 
       FIG. 12C  shows an alternative embodiment of subdermal electrode shield  1800 . As seen in  FIG. 11B , battery B or pulse generator G have electrical lines which are electrically interconnected, also referred to as electrical communication, with a deep brain stimulating probe. These lines are connected such that they allow a deep brain-stimulating probe to provide electrical current to an electrode or placode. As described above, the electrode or placode can thereby generate an electrical field that is preferably positioned such that when energized, the electrical field stimulates a selected portion of the brain and thereby provides therapeutic value. 
       FIG. 12C  shows subdermal electrode shield  1800 . Subdermal electrode shield  1800  includes case  1802 , battery line entry ports  1804  and mouths  1807 . As seen in  FIG. 12C , electrode shield  1800  may have multiple ports  1804  such that the lines  114  from battery B, or pulse generator G, are in electrical communication, also referred to as electrically interconnected, with lines from the battery B or pulse generator G. Lines  114  are spooled though shield  1800  and can exit via mouths  1807 . It should be noted that lines  114  from battery B or pulse generator G could interconnect through a plug  1805 . In the preferred embodiment, plug  1805  is centrally located on an exterior surface of shield  1800 , as seen in  FIG. 12D . 
       FIG. 12E  shows a cross-sectional view of shield  1800 . 
       FIG. 12F  shows an alternative embodiment of shield  1800  wherein the shield  1800  opens and closes in a “clam shell” type arrangement. 
       FIG. 12  G shows an alternative embodiment of shield  1800  wherein the case  1802  is generally rectangular in shape. 
       FIG. 12H  shows an alternative embodiment of shield  1800  where lines  1806  enter shield  1800  via plug  1805 . 
       FIG. 12I  shows an alternative embodiment of shield  1800  where the lines  114  are guided, also referred to as directed, by channels. 
       FIG. 12J  shows a cross-sectional view of shield  1800  seen in  FIG. 12I . As seen in  FIGS. 12I and 12J , lines  114  are not in a nautilus-type circular pattern. It should be noted that the embodiment seen in  FIGS. 12I and 12J  is probably preferable to the embodiments where lines  114  are spooled (arranged in a generally circular fashion) [ FIGS. 12 ,  12 A and  12 B] because when these lines  114  are spooled, an MRI machine&#39;s magnetic field could potentially energize lines  114  which would energize the attached electrode or a placode that has been placed in a patient&#39;s brain to deliver treatment. This uncontrolled energizing of the electrode or placode could damage the brain. 
     As also seen in  FIGS. 12I and 12J , electrode shield  1800  may have multiple ports  1804  such that the lines  114  from battery B, or pulse generator G, are in electrical communication, also referred to as electrically interconnected, with lines from the battery B or pulse generator G. Lines  114  pass through and can exit via mouths  1807 . It should be noted that lines  114  from battery B or pulse generator G could interconnect through a plug  1805 . In the preferred embodiment, plug  1805  is centrally located on an exterior surface of shield  1800 , as seen in  FIG. 12H . 
       FIG. 12J  shows a view of an alternative embodiment of shield  1800  that can accommodate thick lines  1806  or, alternatively, a thick extension kit from battery B or pulse generator G. 
       FIG. 12J  shows a cross-sectional view shield  1800  seen in  FIG. 12I . As seen in  FIG. 12J , case  1802  is preferably generally rectangular. Lines  114  extend therethrough channels  1810 . Channels  1810  are preferably sized to snugly contain lines  114 . Lines  114  exit case  1802  through mouths  1807 . 
       FIGS. 12K ,  12 L,  12 M and  12 N show that shield  1800  can be formed in a variety of shapes. For example, generally rectangular, as seen in  FIG. 12K .  FIG. 12L  shows shield  1800  having a generally curved bottom that is preferably curved to generally conform to the shape of the human skull. The shield in  FIG. 12M  is generally circular in shape.  FIG. 12N  is generally oval in shape. 
       FIG. 12O  shows an alternative embodiment of shield  1800 . As discussed above, shield  1800  is implanted under the patient&#39;s scalp or other subcutaneous area. It is believed that the scalp or other subcutaneous tissue will generally hold shield  1800  so that it does not move relative to the position where the surgeon has initially placed it. However, in order to more fixedly position shield  1800 , anchors  1820  may be positioned on the exterior. As seen in  FIG. 12O , anchors  1820  preferably have loops  1822 . Loops  1822  permit a surgeon to fasten shield  1800  to a patient&#39;s tissue. A variety of sutures, including natural and synthetic, absorbable and nonabsorbable, and monofilament and multifilament sutures could be used to fixedly fasten shield  1800  to a patient. 
       FIG. 12P  is a detailed view of a portion of the shield seen in  FIG. 12O . As shown in  FIG. 12P , mouths  1807  may also include gaskets collars  1825 . Gasket collars  1825  minimize or reduce the movement of material from outside shield  1800  to inside shield  1800 . 
     It should be noted that shields  1800  could have exterior surfaces that are smooth or rough, rigid or soft. It is also believe that if shield  1800  is formed from a bioabsorbable material that the lines  114  would be retained in position by the surrounding tissue after shield  1800  was absorbed by the patient&#39;s body. However, shield  1800  would have to be sufficiently durable such that the patient&#39;s body would have sufficient time to encompass shield  1800  such that it would not move relative to its initial positioning. 
     Among the bioabsorbable materials that shield  1800  may be formed from are: Polyethylene Terephthalate (PET), Polypropylene (PP), Polyetheretherketones (PEEK), High-performance polyethylenes (UHMWPE), Bioabsorbable polymers such as PGA, PLLA or PCL, Various copolymers, Radiopaque materials, Low-friction polymers, Titanium, Nitinol, Stainless Steel or Hybrid biomaterial combinations. In addition, other polymers produced by Pursorb, which manufactures medical grade bioabsorbable materials, which are formed from polymers for medical devices, and are also bioabsorbable and may be appropriate to form shield  1800  are bioabsorbable materials such as: Poly (L-lactide), Poly (D-lactide), Poly (DL-lactide), Polyglycolide, Polycaprolactone, L-lactide/DL-lactide, L-lactide/D-lactide, L-lactide/Glycolide, Lactide/Caprolactone or DL-lactide/Glycolide 
     While the invention has been illustrated and described in detail in the drawings and description, the same is to be considered as an illustration and is not limited to the exact embodiments shown and described. All equivalents, changes and modifications that come within the spirit of the invention are also protected by the claims that are set forth below.