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.
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0. 23. A method, comprising:
selectively blocking conduction of an action potential in a nerve in an animal by selectively, repetitively delivering a series of bi-phasic pulses to the nerve,
where a member of the series of the bi-phasic pulses has a first phase and a second phase, the first phase having a first polarity, a first duration, and a first amplitude, the first phase being a cathodic, depolarizing phase,
the second phase having a second polarity, a second duration, and a second amplitude, the second phase being an anodic, repolarizing phase,
each of the first phase and the second phase being delivered at a frequency in the range of at least 5 KHz up to 10 KHz,
where the ratio of the first amplitude to the second amplitude is 1:1 to 1:5, and
where the first duration is greater than the second duration.
0. 17. A method, comprising:
selectively blocking conduction of an action potential in a nerve in an animal by selectively, repetitively delivering a series of bi-phasic pulses to the nerve,
where a member of the series of the bi-phasic pulses has a first phase and a second phase, the first phase having a first polarity, a first duration, and a first amplitude, the first phase being a cathodic, depolarizing phase,
the second phase having a second polarity, a second duration, and a second amplitude, the second phase being an anodic, repolarizing phase,
each of the first phase and the second phase being delivered at a frequency in the range of at least 5 KHz up to 10 KHz,
where the ratio of the first amplitude to the second amplitude is 1:1 to 1:5, and
selectively blocking conduction of action potentials in progressively smaller nerve fibers in the nerve by altering, over a period of time, one or more of the first amplitude and the second amplitude.
0. 15. A method, comprising:
generating a steady state electrical waveform,
where the steady state electrical waveform has a first phase having a first polarity, a first duration, and a first amplitude, the first phase being a cathodic, depolarizing phase configured to depolarize a nerve,
where the steady state electrical waveform has a second phase having a second polarity, a second duration, and a second amplitude, the second phase being an anodic, repolarizing phase configured to repolarize the nerve,
where the ratio of the first amplitude to the second amplitude is 1:1 to 1:5,
where each of the first phase and the second phase has a frequency in the range of 5 kiloHertz (KHz) up to 10 KHz, and
applying an electric current to the nerve in an animal according to the steady state waveform, where applying the electric current comprises:
selectively, repetitively, alternately applying the first phase of the steady state electrical waveform to the nerve and then applying the second phase of the steady state electrical waveform to the nerve for a period of time sufficient to arrest signal transmission through the nerve, and
arresting signal transmission in progressively smaller nerve fibers in the nerve by altering, over time, at least one of the first amplitude and the second amplitude.
0. 1. A method for selectively blocking activity of a nerve in an animal by application of an electric current, said method comprising: generating an electrical waveform having a first phase with a first polarity, a first duration, and a first amplitude, that produces subthreshold depolarization of the nerve membrane and a second phase after the first phase that has a second polarity, a second duration, and a second amplitude; and applying the waveform to a targeted nerve region, wherein the phases of said waveform are delivered at a rate of at least 5 kilohertz (kHz), and the ratio of the amplitude of the second phase to the amplitude of the first phase is about 1:1 to about 1:5.
0. 2. The method as set forth in
0. 3. The method as set forth in
0. 4. The method as set forth in
0. 5. The method as set forth in
0. 6. The method as set forth in
0. 7. The method as set forth in
0. 8. A method for selectively blocking conduction of an action potential in a nerve of an animal such as a human, said method comprising: delivering an electrical waveform to a nerve, said waveform comprising a series of bi-phasic pulses that, when applied to said nerve, block conduction of an action potential by said nerve, wherein said nerve comprises h gates and m gates and wherein said bi-phasic pulses of said waveform close said h gates and said m gates sufficiently to block said nerve from conducting said action potential, wherein each pulse of said electrical waveform comprises: a first phase having a first polarity, a first duration and a first amplitude, said first amplitude less than an activation threshold of said nerve; and, a second phase having a second polarity, a second duration and a second amplitude, wherein the pulses of said waveform are delivered at a rate of at least 5 kilohertz (kHz), and the ratio of the amplitude of the second phase to the amplitude of the first phase is about 1:1 to about 1:5.
0. 9. The method as set forth in
0. 10. The method as set forth in
0. 11. The method as set forth in
0. 12. The method as set forth in
0. 13. The method as set forth in
0. 14. The method as set forth in
0. 16. The method of claim 15, where the first amplitude is about 0 milliamps to 1 milliamps.
0. 18. The method of claim 17, where the first duration is greater than the second duration.
0. 19. The method of claim 17, comprising:
acquiring, from the animal, one or more of, electroneurogram (ENG) data, and electromyogram (EMG) data; and
configuring the electrical waveform as a function of one or more of, the ENG data, and the EMG data.
0. 20. The method of claim 17, where selectively blocking conduction of the action potential down regulates neural activity in the animal.
0. 21. The method of claim 20, comprising down regulating neural activity in an amount sufficient to treat a disease or condition.
0. 22. The method of claim 21, the disease or condition being one of, neuroma, spasticity, and muscle spasms.
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atfail fall within the meaning and range of equivalency of the claims are therefore intended to be embraced by the claims.
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
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
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
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
II. The Pulse Controller
The pulse controller 14 is desirably housed in a compact, lightweight, hand held housing 28 (see
A. The Desired Electrical Stimulation Waveform
The waveform 34 that embodies features of the invention is shown in
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
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
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
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
A system 10 such as shown in
A system 10 like that shown in
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.
A system 10 like that shown in
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.
Grill, Warren M., McIntyre, Cameron C., Kilgore, Kevin L., Mortimer, John T.
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