Patent Abstract:
Systems and methods for blocking nerve impulses use an implanted electrode located on or around a nerve. A specific waveform is used that causes the nerve membrane to become incapable of transmitting an action potential. The membrane is only affected underneath the electrode, and the effect is immediately and completely reversible. The waveform has a low amplitude and can be charge balanced, with a high likelihood of being safe to the nerve for chronic conditions. It is possible to selectively block larger (motor) nerve fibers within a mixed nerve, while allowing sensory information to travel through unaffected nerve fibers.

Full Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
   This application is a national stage filing under 35 U.S.C. 371 of International Application PCT/US02/04887, filed Feb. 20, 2002, which claims priority from U.S. Application Ser. No. 60/269,832, filed Feb. 20, 2001, the specifications of each of which are incorporated by reference herein. International Application PCT/US02/04887 was published under PCT Article 21(2) in English. 

   FIELD OF THE INVENTION 
   This invention relates to systems and methods for selectively blocking nerve activity in animals, including humans, e.g., to reduce the incidence or intensity of muscle spasms, treat spacticity, or for pain reduction. 
   BACKGROUND OF THE INVENTION 
   Spinal cord injury can lead to uncontrolled muscle spasms. Spasticity can also occur as a result of stroke, cerebral palsy and multiple sclerosis. Peripheral nerve injury can cause pain, such as neuroma pain. 
   Various nerve blocking techniques have been proposed or tried to treat spasms, spacticity, and pain. They have met with varying degree of success. Problems have been encountered, such as damage and destruction to the nerve, and the inability to achieve a differentiation of nerve blocking effects among large and small nerve fibers in a whole nerve. 
   SUMMARY OF THE INVENTION 
   The invention provides systems and methods for blocking nerve impulses using an implanted electrode located near, on, or in a nerve region. A specific waveform is used that causes the nerve membrane to become incapable of transmitting an action potential. The effect is immediately and completely reversible. The waveform has a low amplitude and can be charge balanced, with a high likelihood of being safe to the nerve for chronic conditions. It is possible to selectively block larger (motor) nerve fibers within a mixed nerve, while allowing sensory information to travel through unaffected nerve fibers. 
   The applications for a complete non-destructive nerve block are many. A partial or complete block of motor fiber activity can be used for the reduction of spasms in spinal cord injury, and for the reduction of spasticity in stroke, cerebral palsy and multiple sclerosis. A complete block of sensory input, including pain information, can be used as a method for pain reduction in peripheral nerve injury, such as neuroma pain. A partial or complete block of motor fiber activity could also be used in the treatment of Tourette&#39;s Syndrome. 
   Other features and advantages of the inventions are set forth in the following specification and attached drawings. 

   
     BRIEF DESCRIPTION OF THE DRAWINGS 
       FIG. 1  is block diagram of a system that serves to generate a waveform that stimulates a targeted nerve region to cause either a partial or complete block of motor nerve fiber activity; 
       FIG. 2  is block diagram of an alternative embodiment of a system that serves to generate a waveform that stimulates a targeted nerve region to cause either a partial or complete block of motor nerve fiber activity; 
       FIG. 3  is an enlarged view of a pulse controller that can be used in association with the system shown in  FIG. 1  or  FIG. 2 , the pulse controller including a microprocessor that generates the desired stimulation waveform; 
       FIG. 4  is a graph showing the shape of the stimulation waveform that embodies features of the invention, which is constant current and delivered through at electrode near the nerve and comprises a depolarizing cathodic pulse for blocking nerve conduction immediately followed by an anodic pulse; 
       FIG. 5  is a diagram depicting the presumed action of the voltage controlled sodium ion gates during propagation of an action potential along a nerve. The top trace shows the transmembrane potential and the bottom trace shows the activity of the sodium gates during the same time period. The action potential begins when the m gates, which have a fast response time, open completely. The h gates, which respond more slowly, begin to close, which begins to restore the transmembrane potential. As the potential decreases, the m gates close and the h gates return to their resting position (partially open); 
       FIG. 6  is a diagram showing the action of the depolarizing waveform shown in  FIG. 4 , which is also shown in  FIG. 6  below the upper graph, on the nerve membrane dynamics. The first cathodic, pulse causes the h gate to close and the m gate to open slightly. The anodic phase, which is shorter in duration, causes the m gate to return to the fully open state, but the h gate, because it responds more slowly, does not return completely to its resting value. As subsequent pulses are delivered, the h gate progressively closes, which causes the membrane to become inactivated. When the h gate is sufficiently closed, the nerve membrane can no longer conduct an action potential; and 
       FIG. 7  is a diagram depicting the progressive block of two different nerve fiber diameters, the larger fiber responding to the lower amplitude depolarizing pulse (shown in the lower half of the diagram). The h gate is closed by this waveform and the large nerve fiber becomes inactive. The stimulus amplitude can then be increased so that inactivation of the smaller fiber can take place. 
   

   The invention may be embodied in several forms without departing from its spirit or essential characteristics. The scope of the invention is defined in the appended claims, rather than in the specific description preceding them. All embodiments that fail within the meaning and range of equivalency of the claims are therefore intended to be embraced by the claims. 
   DESCRIPTION OF THE PREFERRED EMBODIMENTS 
   The various aspects of the invention will be described in connection with providing nerve stimulation to cause the blocking of the transmission of action potentials along a nerve. That is because the features and advantages that arise due to the invention are well suited to this purpose. Still, it should be appreciated that the various aspects of the invention can be applied to achieve other objectives as well. 
   I. System Overview 
     FIG. 1  shows a system  10  that makes possible the stimulation of a targeted nerve region N to cause either a partial or complete block of motor nerve fiber activity, which is non-destructive and immediately reversible. In use, the system  10  generates and distributes specific electrical stimulus waveforms to one or more targeted nerve regions N. The stimulation causes a blocking of the transmission of action potentials in the targeted nerve region N. The stimulation can be achieved by application of the waveforms near, on, or in nerve region, using, e.g., using a nerve cuff electrode, or a nerve hook electrode, or an intramuscular electrode, or a surface electrode on a muscle or on the skin near a nerve region. 
   The system  10  comprises basic functional components including (i) a control signal source  12 ; (ii) a pulse controller  14 ; (iii) a pulse transmitter  16 ; (iv) a receiver/stimulator  18 ; (v) one or more electrical leads  20 ; and (vi) one or more electrodes  22 . 
   As assembled and arranged in  FIG. 1 , the control signal source  12  functions to generate an output, typically in response to some volitional action by a patient, e.g., by a remote control switching device, reed switch, or push buttons on the controller  14  itself. Alternatively, the control signal source  12  can comprise myoelectric surface electrodes applied to a skin surface, that, e.g., would detect an impeding spasm based upon preestablished criteria, and automatically generate an output without a volitional act by a patient. 
   In response to the output, the pulse controller  14  functions according to preprogrammed rules or algorithms, to generate a prescribed electrical stimulus waveform, which is shown in  FIG. 4 . 
   The pulse transmitter  18  functions to transmit the prescribed electrical stimulus waveform, as well as an electrical operating potential, to the receiver/stimulator  18 . The receiver/stimulator  18  functions to distribute the waveform, through the leads  20  to the one or more electrodes  22 . The one or more electrodes  22  store electrical energy from the electrical operating potential and function to apply the electrical signal waveform to the targeted nerve region, causing the desired inhibition of activity in the nerve fibers. 
   The basic functional components can be constructed and arranged in various ways. In a representative implementation, some of the components, e.g., the control signal source  12 , the pulse controller  14 , and the pulse transmitter  16  comprise external units manipulated outside the body. In this implementation, the other components, e.g., the receiver/stimulator  18 , the leads  20 , and the electrodes  22  comprise, implanted units placed under the skin within the body. In this arrangement, the pulse transmitter  16  can take the form of a transmitting coil, which is secured to a skin surface over the receiver/stimulator  18 , e.g., by tape. The pulse transmitter  16  transmits the waveform and power through the skin to the receiver/stimulator  18  in the form of radio frequency carrier waves. Because the implanted receiver/stimulator  18  receives power from the external pulse controller  14  through the external pulse transmitter  16 , the implanted receiver/stimulator  18  requires no dedicated battery power source, and therefore has no finite lifetime. 
   A representative example of this implementation (used to accomplish functional electrical stimulation to perform a prosthetic finger-grasp function) can be found is in Peckham et al U.S. Pat. No. 5,167,229, which is incorporated herein by reference. A representative commercial implementation can also be found in the FREEHAND™ System, sold by NeuroControl Corporation. (Cleveland, Ohio). 
   In an alternative arrangement (see  FIG. 2 ), the leads  20  can be percutaneously installed and be coupled to an external interconnection block  24  taped to the skin. In this arrangement, the pulse transmitter  16  is directly coupled by a cable assembly  26  (see  FIG. 3 , also) to the interconnection block  24 . In this arrangement, there is no need for a pulse transmitter  16  and receiver/stimulator  18 . A representative commercial example of this implementation (used to achieve neuromuscular stimulation to therapeutically treat shoulder subluxation and pain due to stroke) can be found in the StIM™ System, sold by NeuroControl Corporation (Cleveland, Ohio). 
   II. The Pulse Controller 
   The pulse controller  14  is desirably housed in a compact, lightweight, hand held housing  28  (see  FIG. 3 ). The controller  14  desirably houses a microprocessor  30 . Desirably, the microprocessor  30  carries imbedded code, which expresses the pre-programmed rules or algorithms under which the desired electrical stimulation waveform is generated in response to input from the external control source  12 . The imbedded code can also include pre-programmed rules or algorithms that govern operation of a display and keypad on the controller  14  to create a user interface  32 . 
   A. The Desired Electrical Stimulation Waveform 
   The waveform  34  that embodies features of the invention is shown in  FIG. 4 . A stimulus provided by this waveform  34  is delivered to a nerve N through the electrodes  22  located on or around the nerve N. The waveform  34 , when applied, places the nerve fiber membrane into a state in which it is unable to conduct action potentials. 
   The specific electrical stimulus waveform  34  that can be applied to cause a blocking of the transmission of action potentials along the nerve has two phases  36  and  38  (see  FIG. 4 ). 
   The first phase  36  produces subthreshold depolarization of the nerve membrane through a low amplitude cathodic pulse. The first phase  36  can be a shaped cathodic pulse with a duration of 0.1 to 1000 millisecond and a variable amplitude between 0 and 1 milliamp. The shape of the pulse  36  can vary. It can, e.g., be a typical square pulse, or possess a ramped shape. The pulse, or the rising or falling edges of the pulse, can present various linear, exponential, hyperbolic, or quasi-trapezoidal shapes. 
   The second phase  38  immediately follows the first pulse  36  with an anodic current. The second anodic phase  38  has a higher amplitude and shorter duration than the first pulse  36 . The second pulse  38  can balance the charge of the first phase  36 ; that is, the total charge in the second phase  38  can be equal but opposite to the first phase  36 , with the second phase having a higher amplitude and shorter duration. However, the second pulse  38  need not balance the charge of the first pulse  36 . The ratio of the absolute value of the amplitudes of the second phase  38  compared to the first phase  36  can be, e.g., 1.0 to 5.0. Because of the short duration of the anodic phase  38 , the nerve membrane does not completely recover to the non-polarized state. 
   This biphasic pulse is repeated continuously to produce the blocking stimulus waveform. The pulse rate will vary depending on the duration of each phase, but will be in range of 0.5 Hz up to, 10 KHz. When this stimulus waveform  34  is delivered at the appropriate rate, typically about 5 kHz, the nerve membrane is rendered incapable of transmitting an action potential. This type of conduction block is immediately reversible by ceasing the application of the waveform. 
   Larger nerve fibers have a lower threshold for membrane depolarization, and are therefore blocked at low stimulus amplitudes. As a result, it is possible to block only the largest nerve fibers in a whole nerve, while allowing conduction in the smaller fibers. At higher stimulus amplitudes, all sizes of fibers can be blocked completely. 
   The physiological basis on which the waveform  34  is believed to work can be described .using the values of the sodium gating parameters, as shown in  FIG. 5 . The unique ability of the nerve axon to transmit signals is due to the presence of voltage controlled ion channels. The function of the sodium ion channels are influenced by two gates. One gate responds quickly to voltage changes, and is frequently termed the “m” gate. The other gate responds more slowly to voltage changes, and is termed the “h” gate. When the nerve is in, the rest condition, the m gates are almost completely closed, while the h gates are partially opened. When an action potential propagates along the axon, the m gates open rapidly, resulting in a rapid depolarization of the nerve membrane. The h gates respond by slowly closing. The membrane begins to repolarize, and the m gates begin to close rapidly. At the end of action potential generation, the m gates have returned to their initial state and the nerve membrane is slightly more polarized than at rest. The h gates return more slowly to their resting values, producing a period of reduced excitability which is referred to as the refractory period. The same series of events can be initiated by an externally applied cathodic (depolarizing) stimulus pulse. This is the basis for electrical stimulation of nerves. 
   The waveform  34  of the invention makes use of the different relative responses of the two types of sodium ion channel gates. The first phase  36  of the waveform  34  is a subthreshold depolarizing pulse. The nerve membrane response is shown in  FIG. 6 . The h gates begin to slowly close during the first phase, while the m gates respond by opening only slightly. As long as the initial phase is maintained below the activation threshold for the nerve, the m gates will exhibit only a small response. If the depolarizing pulse  36  is maintained for long periods of time, the h gates will eventually close to the point that the membrane is no longer able to transmit an action potential. 
   The second phase  38  of the waveform  34  is a hyperpolarizing pulse of shorter duration than the initial depolarizing pulse. The effect of this pulse  38  is to cause the m gates to close completely and the h gates begin to slowly open. However, since this phase  38  is shorter than the first phase  36 , the h gates do not return to their resting levels by the end of the phase  38 . A second pulse of the waveform  34  of the same shape is then delivered to the nerve. The depolarization of the first phase  36  results in further closing of the h gates, with slight opening of the m gates. Some opening of the h gates again occurs with the second hyperpolarizing phase  38  of the pulse, but recovery back to the initial value does not occur. With subsequent pulses, the h gate progressively nears complete closing, while the m gate varies slightly between fully closed and slightly open. Due to the dynamics of the h gate, it will not fully close, but will continue to oscillate with each pulse near the fully closed condition. With both the m gate and the h gate nearly closed, the nerve membrane is now incapable of conducting action potentials. The nerve is effectively blocked. 
   This block can be maintained indefinitely by continuously delivering these pulses to the nerve. The block is quickly reversible when the stimulation is stopped. The h and m gates will return to their resting values within a few milliseconds, and the nerve will again be able to transmit action potentials. 
   Larger nerve fibers will have a lower threshold for subthreshold depolarizing block. Therefore, when the blocking waveform is delivered to a whole nerve, only the largest nerve fibers will be blocked. This provides a means of selective block, allowing a block of motor activation without affecting sensory information, which travels along the smaller nerves. 
   In order to generate a block of smaller nerve fibers in a large nerve, the amplitude of the waveform can be increased. As the amplitude is increased, the first phase of the waveform may produce a stimulated action potential in the larger nerves. However, because of the nerve membrane dynamics, it is possible to gradually increase the stimulus amplitude over time with each successive pulse, until even the smallest nerve fibers are blocked. This, is shown in  FIG. 7 . Very low amplitude pulses are used to put the membrane of the largest nerve fibers into an unexcitable state over the course of a few pulses. Once these largest fibers are at a steady state, they will not be activated even by very large cathodic pulses. At this point, the blocking stimulus amplitude can be increased so that it produces the closed h and m gate response in the smaller nerve fibers. The amplitude can be progressively increased until all nerve fibers are blocked. This progressive increase can occur rather quickly, probably within a few hundred milliseconds. This mechanism also serves to underscore the possibility of selective blocking of fibers of largest size using this waveform. 
   EXAMPLE 1 
   Neuroma Pain 
   A system  10  such as shown in  FIG. 1  can be used to block neuroma pain association with an amputated arm of leg. In this arrangement, one or more electrodes  22  are secured on, in, or near the neuroma. The pulse controller  14  can comprise a handheld, battery powered stimulator having an on-board microprocessor. The microprocessor is programed by a clinician to generate a continuous waveform that embodies features of the invention, having the desired amplitude, duration, and shape to block nerve impulses, in the region of the neuroma. The pulse controller  14  can be coupled to the electrode, e.g., by percutaneous leads, with one channel dedicated to, each electrode used. A control signal source  12  could comprise an on-off button on the stimulator, to allow the individual to suspend or continue the continuous application of the waveform, to block the neuroma pain. No other special control functions would be required. 
   EXAMPLE 2 
   Muscle Spasms Due to Spinal Cord Injury, Cerebral Palsy, or Tourett&#39;s Syndrome 
   A system  10  like that shown in  FIG. 1  can be used to block muscle spasms due to, e.g., a spinal cord injury, cerebral palsy, or tourett&#39;s syndrome. In this arrangement, one or more electrodes  22  are secured on, in, or near the nerve or nerves affecting the muscle spasms. As in Example 1, the pulse controller  14  can comprise a handheld, battery powered stimulator having an on-board microprocessor. The microprocessor is programed by a clinician to generate a continuous waveform that embodies features of the invention, having the desired amplitude, duration, and shape to block nerve impulses in the region of the muscle spasms. As in Example 1, the pulse controller  14  can be coupled to the electrode, e.g., by percutaneous leads, with one channel dedicated to each electrode used. A control signal source  12  could comprise an on-off button on the stimulator, to allow the individual to suspend or continue the continuous application of the waveform, to block the muscle spasms. Thus, for example, the individual could turn the stimulator off during sleep, or during a period where muscle function is otherwise desired. The selective stimulation-off feature also allows the individual to perform muscle functions necessary to maintain muscle tone. In this arrangement, no other special control functions would be required. 
   Alternatively, the control signal source  12  could comprise an electrode to sense electroneurogram (ENG) activity in the region where muscle spasms occur. The electrode could comprise the stimulation electrode itself, or a separate ENG sensing electrode. The electrode detects ENG activity of a predetermined level above normal activity (e.g., normal ENG activity X10), identifying a spasm episode. In this arrangement, the microprocessor is programed to commence generation of the desired waveform when the above normal ENG activity is sensed. The microprocessor is programmed to continue to generate the waveform for a prescribed period of time (e.g., 1 minute) to block the spasm, and then cease waveform generation until another spasm episode is detected. In this arrangement, the stimulator can also include a manual on-off button, to suspend operation of the stumulator in response to input from the sensing electrode. 
   EXAMPLE 3 
   Block Uncoordinated Finger Flexure Spasms Due to Multiple Sclerosis or Stroke 
   A system  10  like that shown in  FIG. 1  can be used to block finger flexure spasms due to, e.g., a multiple sclerosis or stroke. In this arrangement, one or more epimysial and intramuscular electrodes  22  are appropriately implanted by a surgeon in the patient&#39;s arm. The implanted electrodes  22  are positioned by the surgeon by conventional surgical techniques to block conduction of impulses to finger flexure muscles. As in Example 1, the pulse controller  14  can comprise a handheld, battery powered stimulator having an on-board microprocessor. The microprocessor is programed by a clinician to generate a continuous waveform that embodies features of the invention, having the desired amplitude, duration, and shape to provide a low level block of nerve impulses to the finger flexure muscles. A control signal source  12  could comprise an on-off button on the stimulator, to allow the individual to select the continuous application of the waveform, e.g., while the individual is opening or closing their hand. 
   Alternatively, the control signal source  12  could comprise an electrode to sense electromyogram (EMG) activity in the finger flexor muscles. The electrode detects EMG activity during stimulated activation of the finger extensor muscles. If this activity exceeds a preset level (e.g. 30% maximum contraction level), the microprocessor is programmed to commence generation of the desired waveform to block some or all of the finger flexor muscle activity. The microprocessor can be programmed to deliver a block proportional to the level of EMG activity, or to deliver a block for a prescribed period of time, or to deliver a block as determined through a combination of parameters (e.g., EMG activity from multiple muscles in the arm). 
   In another alternative embodiment, the control signal source  12  can comprise comprises a mechanical joy stick-type control device, which senses movement of a body region, e.g., the shoulder. Movement of the body region in one prescribed way causes the microprocessor to commence generation of the desired waveform. Movement of the body region in another prescribed way causes the microprocessor to cease generation of the desired waveform. 
   In either alternative arrangements, the stimulator can also include a manual on-off button, to suspend operation of the stumulator in response to the external inputs. 
   Various features of the invention are set forth in the following claims.

Technology Classification (CPC): 0