US20150112118A1

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Publication number: US20150112118A1
Application number: US14/586,713
Authority: US
Inventors: David J. Mishelevich; M. Bret Schneider
Original assignee: Cervel Neurotech Inc
Current assignee: Rio Grande Neurosciences Inc
Priority date: 2007-08-20
Filing date: 2014-12-30
Publication date: 2015-04-23
Also published as: WO2009026386A1; US8956273B2; AU2008288967A1; JP2010536496A; US20100256438A1; CA2694037A1; EP2183025A1; EP2183025B1

Abstract

Methods, devices and systems for Transcranial Magnetic Stimulation (TMS) are provided for synchronous, asynchronous, or independent triggering the firing multiple of electromagnets from either a single power source or multiple energy sources. These methods are particularly useful for stimulation of deep (e.g., sub-cortical) brain regions, or for stimulation of multiple brain regions, since controlled magnetic pulses reaching the deep target location may combine to form a patterned pulse train that activates the desired volume of target tissue. Furthermore, the methods, devices and systems described herein may be used to control the rate of firing of action potentials in one or more brain regions, such as slow or fast rate rTMS. For example, described herein are multiple electromagnetic stimulation sources, each of which are activated independently to create a cumulative effect at the intersections of the electromagnetic stimulation trajectories, typically by means of a computerized calculation.

Description

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a divisional of U.S. patent application Ser. No. 12/670,938, filed on Jun. 17, 2010, titled “FIRING PATTERNS FOR DEEP BRAIN TRANSCRANIAL MAGNETIC STIMULATION,” Publication No. US-2010-0256438-A1, which is a 35 U.S.C. 371 National Phase Application of International Patent Application No. PCT/US2008/073751, filed on Aug. 20, 2008, titled “FIRING PATTERNS FOR DEEP BRAIN TRANSCRANIAL MAGNETIC STIMULATION,” Publication No.WO 2009/026386, which claims priority to the following applications: U.S. Provisional Patent Application No. 60/956,920, filed on Aug. 20, 2007, titled “FIRING PATTERNS FOR DEEP BRAIN TRANSCRANIAL MAGNETIC STIMULATION;” U.S. Provisional Patent Application No. 60/970,958, filed on Sep. 9, 2007, titled “PULSING MULTIPLE INDEPENDENTLY TRIGGERED ELECTROMAGNETS FROM ONE OR MORE ENERGY SOURCES;” and U.S. Provisional Patent Application No. 61/077,488, filed on Jul. 2, 2008, titled “DIFFERENTIAL PULSE PATTERNS IN PARALLEL STIMULATION ARRAYS.” Each of these applications is herein incorporated by reference in its entirety.

INCORPORATION BY REFERENCE

All publications and patent applications mentioned in this specification are herein incorporated by reference in their entirety to the same extent as if each individual publication or patent application was specifically and individually indicated to be incorporated by reference.

FIELD OF THE INVENTION

The devices and methods described herein relate generally to the triggering of electromagnets used for Transcranial Magnetic Stimulation.

BACKGROUND OF THE INVENTION

Transcranial Magnetic Stimulation (TMS) of the brain has been employed in a limited way to treat depression refractory to the administration of drugs. The number of treatable conditions may significantly increase as the depth of the target increases. Systems for targeting neural structures at depth (e.g., Schneider and Mishelevich, U.S. patent application Ser. No. 10/821,807, now U.S. Pat. No. 7,520,848, and Mishelevich and Schneider, U.S. patent application Ser. No. 11/429,504, now U.S. Pat. No. 8,052,591) may include multiple electromagnets, the firing of which must be coordinated. TMS stimulation of deep targets would potentially permit treatment of a variety of conditions such as chronic pain, addiction, obesity, depression, Alzheimer's disease, and Parkinson's disease. Conventional rTMS (repetitive transcranial magnetic stimulation) is capable of effectively stimulating only the outer cortical layer of the brain, and treats depression indirectly, by stimulating neural pathways that run from the prefrontal cortical surface to the cingulate gyms, rather than hitting the target directly. It is preferable to stimulate deep structures such as the cingulate gyms directly, but when targeting deep neural structures with rTMS, care must be taken to avoid over-stimulating superficial structures to eliminate undesired side effects such as seizures or producing unintended neural-stimulation results. It is thus necessary to avoid having too many successive pulses from the same electromagnet passing through such superficial structures while targeting the deep structure.

To effectively elicit an action potential in a neural structure, adequate stimulation must be received in a time period which is less than the minimum time (usually expressed as chronaxie) that it takes the target neural membrane to re-polarize. Otherwise threshold for generating an action potential will not be achieved. With respect to another time scale, for a given neural structure, stimulating pulses must be received within a maximum effective time interval such that the effect of the generated action potentials is additive. Neural elements are typically highly interconnected and the actual final target element to be stimulated will receive inputs from multiple sources

The pulse-rate frequency from any given electromagnet location is preferably limited, typically to a rate of less than 50 pulses per second (i.e., 50 Hz). While limiting the frequency from a single stimulating location will protect structures superficial to the deeper target, it may be impossible to effectively stimulate a deep target because of the rapid fall off of the magnetic field (roughly 1/(distance)²at short distances). Thus, different trajectories must be stimulated in turn. We have previously suggested accomplishing this by either moving the electromagnets, as is described in Schneider and Mishelevich, U.S. patent application Ser. No. 10/821,807 (“Robotic apparatus for targeting and producing deep, focused transcranial magnetic stimulation”) or by sequentially firing electromagnets located at distributed locations. The approach of this latter case may avoid over-stimulating superficial neural structures at a single location and causing seizures or other undesired impacts, but to be successful, the pulsed magnetic fields must reach the target at a higher effective rate of stimulation than the pulsed magnetic fields hitting superficial tissue. The coordination of the orientation, timing, frequencies and power levels for controlling multiple magnets to stimulate one or more targets, and particularly deep tissue targets is a difficult task that has not yet been effectively accomplished. Described herein are methods, devices and systems for accomplishing this.

Furthermore, different tissues may have differing requirements in terms of the amount of function augmentation or suppression that they require, or that they can tolerate. For example, when seeking to suppress the activity of a remote target using slow rate rTMS delivered from multiple intersecting pathways, one or more intermediate tissues may be inadvertently suppressed in the process, when, in fact, such tissue(s) require functional augmentation.

For example, Isenberg et al., and others, have shown that either fast rate (e.g., 10 Hz) rTMS applied to the left dorsolateral prefrontal cortex (LDLPFC) or slow rate rTMS (e.g., 1 Hz) applied to the right dorsolateral prefrontal cortex (RDLPFC), are effective treatments for depression. Published studies have involved treating either of those two targets. The practical limitations of currently available equipment prevent the alternative or concurrent slow right and fast left treatment. These limitations stem from logistical difficulties in positioning TMS coils, and applying selected pulse parameters at the correct positions.

Arrays of multiple magnetic coils have been proposed. For example, Ruohonen et al. (1998) modeled in software an array of small adjacent magnets intended to stimulate the outer cortical surface of the brain. While power requirements are calculated in this study, no specific means for delivering or switching that power are disclosed. Ruohonen et al. (1999) modeled in software a multi-coil array for the purpose of limb rehabilitation. Again, no specific means for switching or delivering power to the appropriate coil were described. Instead, “the multichannel design allows the stimulus to be moved without moving the coils. This is accomplished by individually adjusting the strength and direction of the current in each coil.” Han et al. (2004) proposed a multiple coil array, but they also had no particular strategy for powering the coils other than turning them on simultaneously, and describes, “[i]n the multichannel magnetic stimulation, it is assumed that the predetermined optimal currents are fed in-phase to the coils. Therefore, all the channels are generally ON state when a stimulation pulse is applied to the subject.”

Thus, there is a need for appropriately controlling the stimulation from magnets so that the stimulation can be focused on deep tissue without creating undesired stimulation or inhibition effects in tissue superficial to the deep target. Furthermore, if effects are to be induced upon the intervening neural structures, those effects should be calculated, controllable, desirable effects. The control of the system must allow powering of the array of magnets by tapping the stored charge from one or more sources, and delivering them precisely, under the appropriate circumstances to each coil, individually. There is also a need for a system by which the pulse rate, power and pattern of stimuli delivered through intermediately juxtaposed brain tissue may be different in the different coils of the array, thereby better suiting the characteristics and therapeutic needs of that intermediate brain tissue as well as that of the principal target. Depending on the number of electromagnets, the capacity of the power sources, and other factors, it may be more appropriate to supply power for the triggering of the electromagnets from either a single power source or multiple power sources. Systems, devices and methods to address these needs, as well as others, are described in greater detail below.

SUMMARY OF THE INVENTION

Described herein are methods, devices and systems for controlling the firing of electromagnets located at different positions to stimulate at least one brain region, including deep brain regions. The firing may be performed at fixed, random, or mixed fixed and random intervals, and/or at different pulse rates. In general, the methods described herein include methods of focusing stimulating from multiple magnets on one or more brain region so that energy from the magnets sums in a desired brain region to trigger firing of neurons (e.g., action potentials) in the target brain regions without triggering firing in adjacent (and particularly superficially located) brain regions. The methods further include controlling the timing, rate, and power of each magnet in an array of magnets to achieve transcranial magnetic stimulation so that energy applied by the magnets to non-target regions is below a threshold for stimulation and energy applied to target regions is above the threshold. Furthermore, the rate of stimulation (e.g., the rate that action potentials are evoked) in target regions may be controlled to modulate the effects of stimulation of a target region.

In one embodiment, one or more pulses can be generated (e.g., 3, 2, 2, 1, 5 pulses etc.) at one location before moving on to the next. Alternatively, some or all the pulses can be concurrently fired from two or more locations. Instead of whole trains of pulses stimulating a given volume of superficial tissue, relatively few pulses per a given period of time may be fired from locations close to, and potentially stimulate the superficial tissues, but the magnetic pulses reaching the deep target location from a plurality of magnets may combine to form a pulse train that activates the desired volume of target tissue. The plurality of electromagnets referred to herein may be in fixed positions or may be mobile (as in Schneider and Mishelevich, U.S. patent application Ser. No. 10/821,807). The net effect at the target location is due to combined elements of temporal and spatial summation.

This approach may also be used to take advantage of the individual properties of different brain regions, permitting each region to be stimulated with the pulse sequence that maximally contributes to the overall intended effect of the treatment. For example, adverse effects may result if pulse rates exceed 3 Hz when the pulse trajectory passes through the right dorsolateral prefrontal cortex on the way to a cingulate target. Consequently, it may benefit the overall treatment strategy to limit the rate of pulses passing through the right dorsolateral prefrontal cortex, even though a faster pulse rate would help the temporal summation effect.

By coordinating the activity of a plurality of electromagnets, each of which must receive a certain amount of pulsed electrical charge at specific times with respect to one another, the devices, methods and systems described herein may control the stimulation of one or more brain regions, including regions previously thought to be too deep for controlled transcranial magnetic stimulation. This process may occur in configurations in which the charge pulses received by these electromagnets are simultaneous, and when the charge delivery among these coils is not simultaneous.

In one variation, a single power source has an output directed to multiple electromagnets by controlling which driver is gated to conduct to a given electromagnet via a distributor element controlled by a stimulation controller. In another variation, multiple power sources (for example, one for each electromagnet) are each controlled via an associated driver. The gating of the drivers is determined by a distributor element controlled by a stimulation controller. Single power source and multiple power source configurations can be mixed in a single system.

These methods, systems and devices may also allow a neuromodulation-produced energy source to simultaneously deliver different effects to different neural tissues. For example, multiple stimulation trajectories or multiple stimulation sources (e.g., TMS coils) may be controlled to achieve targeted stimulation. Each of these sources may be capable of independent function. The cumulative effect of the multiple sources at the intersection of their paths, as well as the independent effects of each source in proximal tissue, are calculated and controlled by the system described.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows five coil-pair sets of electromagnets.

FIG. 2 illustrates one embodiment of a system for stimulating neuronal tissue deep within a subject's brain in which the power for the electromagnets is provided by a single energy source.

FIG. 3 illustrates another embodiment of a system for stimulating neuronal tissue deep within a subject's brain in which the power for the electromagnets is provided by multiple individual energy sources.

FIG. 4 illustrates various forms of control that can be provided for the plurality of coils.

FIG. 5 shows an array of 3 energy sources around a patient's head, shown in frontal external view (left), and in cross section (right).

FIG. 6 is a table that illustrates three variations of ways in which the coils such as those shown inFIG. 5 may be activated in order to achieve a desired effect, including three threshold-based (action-potential-elicited versus no-action-potential-elicited) calculations.

FIGS. 7A and 7B show two exemplary arrays of 4 (double) stimulator coils positioned around a patient's head.

FIG. 8 is a table that tallies the effect of different pulse patterns in the coils shown inFIGS. 7A and 7B in a manner that considers distance from each coil, and the strength of the magnetic pulses (measured continuously rather than as a binary variable), and the resultant effect upon the target structure relative to interposed superficial structures.

FIG. 9 is an flowchart showing one variation of a Transcranial Magnetic Stimulation method, as described herein.

FIG. 10 illustrates distances measured from the bottom of cortical sulci to a deep target, in this example, the cingulate bundle.

FIG. 11 is one variation of a portion of a method of determining stimulation parameters for Transcranial Magnetic Stimulation.

DETAILED DESCRIPTION OF THE INVENTION

The Transcranial Magnetic Stimulation (TMS) methods, devices and systems described herein are capable of triggering action potential (including specified patterns of action potentials) in one or more target brain regions without triggering action potentials nearby non-target regions, including regions that are superficial (e.g., between the target region and the external magnets(s) stimulating the brain). These TMS systems may support a variety of action potential firing patterns by controlling the pulsing of multiple, independently triggerable, electromagnets from one or more energy sources. The system may also monitor or control the one or more power supplies so that there is sufficient capacity from the power supplies so when a given pulse is triggered, adequate power is available to deliver a stimulus from each electromagnet as needed to trigger the desired action potentials from the target brain region.

FIG. 1 illustrates a configuration incorporating five

electromagnets

110,120,130,140, and150 which may be used as part of a TMS system as described herein. The electromagnets need not be of equal size, and do not have to be in a uniform relationship to each other. The electromagnets may move as a group (say on a gantry or robotic arm) and/or in relationship to each other over time. For example, the electromagnets may be moved during stimulation (TMS) or they may be fixed during stimulation. InFIG. 1, a target neural (brain)tissue region170 is illustrated. This region need not be equidistant from the electromagnets. Two or more electromagnets must be included; in the description of the embodiments illustrated inFIGS. 2 and 3, four electromagnets are incorporated.

In general, the devices and systems described herein may be used to stimulate one or more regions of the brain. As used herein “stimulation” of a brain region may refer to the eliciting of one or more (or a series of) action potentials from the brain region. Deep brain regions in particular may be stimulated with these devices and methods. As used herein the phrase “deep brain regions” may refer to cortical and sub-cortical brain regions, or just sub-cortical brain regions (e.g., regions below the subject's cortex). In some variations, multiple brain regions (including a cortical and a sub-cortical brain region, two or more sub-cortical regions, etc.) may be stimulated. For example, a complex pulse rhythm such as the “theta” pattern (Huang et al., 2005) on one region of the brain may facilitate TMS-induced neuromodulation effects in another part of the brain. Thus, the systems described herein may be used to simultaneously stimulate such a pattern in one region while simultaneously stimulating another region.

In order to stimulate one or more brain regions, the TMS systems described herein control the plurality of electromagnets to trigger pulses of an appropriate strength, duration and frequency (including complex patterns of stimulation), at each of the plurality of electromagnets so that only target brain region(s) are activated. Triggering of pulses can be done mechanically (e.g., through notches in a cam) or electronically using a built-in fixed, random, or mixed pattern or such patterns can be generated under computer control.

In general, the system may generate appropriate firing patterns for each of the plurality of electromagnets in the system. The “firing pattern” may refer to the duration of a pulse, the frequency of the pulse, and the intensity (strength) of the pulse (e.g., the current/voltage applied to generate the pulse). The system typically controls and coordinates the firing patterns of all of the electromagnets. For example, the electromagnets may be fired in a sequential order (e.g., first electromagnet, second electromagnet, third electromagnet, etc.) or in some other order (including random or pseudo-random). An example of a sequential firing pattern is shown in Table 1 and of a random firing is shown in Table 2, below. In Table 1, electromagnets at five different locations, A through E represented in the table columns, are triggered sequentially as the process steps throughtimes 1 through 10 represented in the table rows. The objective is to minimize the number of pulses received by tissues close to a given electromagnet to avoid undesirable side effects while maximizing the number of pulses stimulating the target. Each pulse must be of sufficient duration so that the neural membrane will not re-polarize. For example, the chronaxie of a typical cortical neuron is 450 microseconds. The electromagnets are physically distributed such that tissues close to one electromagnet location (e.g., location “A”) will be little impacted by pulses from a different location (location “B”). In Table 1, for location A, pulses may be triggered attime steps 1 and 6, so at the end oftime step 10, two pulses have passed through neural tissue from the electromagnet at location A. The same effect will be true for electromagnets at locations B through E. The common target, however will have received a pulse at each time step, albeit at a somewhat lower magnitude because it is further away than tissues close to the electromagnets at locations A through E. As demonstrated, at the end of 10 time steps, tissues near the individual electromagnet locations A through E will have received only two pulses where the target deep location will have received ten pulses.

TABLE 1

SEQUENTIAL FIRING PATTERN

LOCATION

TIME	A	B	C	D	E	TARGET

1	1					1
2		1				1
3			1			1
4				1		1
5					1	1
6	1					1
7		1				1
8			1			1
9				1		1
10					1	1
CUM	2	2	2	2	2	10
TOTALS

The TMS systems described herein may include control logic that coordinates the firing pattern, as well as the timing, strength and duration of the pulses applied by the electromagnets. This control logic (which may be part of a controller, and may be hardware, software, or both) may receive inputs regarding the subject's target anatomy (e.g., the location of one or more targets relative to the electromagnets), as well as information regarding the status of the power supply(s) indicating available power. Finally, inputs such as the desired rate of evoked action potentials for a target region may also be included. Additional inputs may be used as well. These inputs may help the control logic to determine the stimulation at each of the electromagnets, including what the firing pattern should be.

An example of a random firing pattern is demonstrated in Table 2. In this example, the same net number of pulses is delivered to tissues close to the electromagnets at locations A through E while the deep target receives 10 pulses, similar to the pattern shown in Table 1. Sequential and random firing patterns can be mixed to produce the same results, and more than one pulse can be triggered at a given time step before moving on to the next time step. Some or all the pulses can be simultaneously fired from two or more locations.

TABLE 2

RANDOM FIRING PATTERN

LOCATION

TIME	A	B	C	D	E	TARGET

1		1				1
2				1		1
3	1					1
4					1	1
5				1		1
6		1				1
7			1			1
8	1					1
9		1				1
10					1	1
CUM	2	3	1	2	2	10
TOTALS

The time interval betweentime steps 1 through n may be tailored to deliver the pulses at a rate that is faster than the interval at which the target neural elements (neurons of the target brain region) will re-polarize; at this faster rate, the threshold for the target neural elements will be exceeded and desired effective stimulation may occur, triggering an action potential. The firing rate of the individual electromagnets at locations A through n (and thus the combined pulse rate that will be delivered at the target location) depends on the number of those individual electromagnets. For example, to achieve a pulse rate at the target to be 1000 Hz, if there are five individual electromagnets (e.g., A through E), this can be achieved by stimulating those five electromagnets at an effective rate of about 200 Hz each. If there are three only individual electromagnets (e.g., A through C), this can be achieved by stimulating those five electromagnets at an effective rate about 333 Hz each. All of the electromagnets need not be fired at the same frequency to achieve the effect. For example to get a pulse rate of 1000 Hz at the target, two of three electromagnets could have an effective firing rate of 400 Hz and the third could have an effective firing rate of 200 Hz. It is also not necessary that the electromagnets be of uniform type or size. In any situation involving random firing, the time interval can vary as well as the firing sequence.

The system may also control the firing pattern in order to achieve a desired rate of stimulation of the target tissue (e.g., a rate of action potential firing). For example, the system may control the electromagnets so that high pulse rates (e.g., 1000 Hz) may be achieved for only a fraction of a second, for example over 5 successive pulses, closely spaced, one from each of 5 electromagnets, followed by a pause. In such a case, the “1000 Hz” pulse burst may be experienced by neurons as a single stimulation. Provided that a sufficient period of wait (e.g., 0.2 seconds) separates the rapid (e.g. 1000 Hz) multi-electromagnet bursts, the net effect experienced by a deep target tissue will of a much slower pace, for example, between 5-50 Hz. The same principle may be applied to the production of temporally summated multi-electromagnet bursts in the production of slow-rate or fast-rate rTMS. For example, even if 5 electromagnet are discharged once each at a 1000 Hz rate, so long as about 1 second separates the overlapping bursts (e.g., the bursts summed in the target tissue), the effective pulse rate and safety profile experienced by a given brain part will be just short of 1 Hz. Thus, by firing each electromagnet once, each in rapid (e.g., 1000 Hz) succession (a “burst”), but then waiting 0.2 seconds to 1 second between bursts, we can get temporal summation and the safety of normal rTMS rates.

The TMS systems described herein may therefore attend to the overall stimulation pattern while controlling each electromagnet (or groups of electromagnets) individual firing rates, durations and strengths. In general, the stimulation of target tissue results from the temporal and spatial summation of the effect of the applied electromagnetic field at the target tissue. Thus, the system determines the appropriate firing pattern for all of the electromagnets as well as the individual firing (strength, duration and rate) for each electromagnet so that the firing of each electromagnet results in a sub-threshold energy for the non-target tissue, but the focused energy on the target tissue is above-threshold. As indicated, controlling the power applied by the system is one part of this control. In general, each electromagnet may be powered by a single power source, multiple power sources, or one power source may be used to power multiple electromagnets.

FIG. 2 illustrates an embodiment of a TMS system in which power for the electromagnets is provided by a single energy source. One output ofpower source200 is provided in common viaconnection220 to all of theelectromagnets230. While fourelectromagnets230 are shown in the figure, any number feasible in the applied geometry can be powered. The firing of the individual electromagnets is determined bystimulation controller250, which activatesdistributor260 to select theappropriate driver280 which when selected at the given time delivers power viaconnection210 frompower source200 to the associatedelectromagnet230 viaconnection290.

FIG. 3 illustrates an embodiment in which power for the electromagnets is provided by individual power sources. One output of all the power sources (e.g., power sources A through D)300,302,304,306 is provided in common byconnection320 to all the

electromagnets

330,332,334,336. Although four

electromagnets

330,332,334,336 are shown in the figure, any number of electromagnets feasible to the applied geometry can be powered. The firing of the individual electromagnets in this example determined bystimulation controller350, which activatesdistributor360 to select the appropriate driver (e.g., drivers A through D)380,382,384, or386 which when selected at the given time delivers power via associated

connection

390,392,394 or396 from

respective power source

300,302,304 or306 to the associated

electromagnet

330,332,334 or336. Thecontroller350 may run the control logic coordinating the stimulation of the target while avoiding stimulation of non-target regions.

In either variation illustrated inFIG. 2 andFIG. 3, more than a single electromagnet can be pulsed simultaneously, so long as the power source (e.g.,FIG. 2) or power sources (e.g.,FIG. 3) have sufficient capacity. As mentioned, the control logic may determine the appropriate output based on the available capacity of the power source(s). This capacity may be monitored directly (e.g., by one or more inputs), based on specification, or based on calculation or estimate.

FIG. 4 illustrates various examples of control of the firing pattern and excitation of the electromagnets (coils) that can be provided for the plurality of coils in accordance with the present invention as above described.Electromagnet charge storage400 may be divided intoSingle Source methods410 andMultiple Source methods420.Single Source methods410 may be subdivided into categories, as shown inFIG. 4. SingleSource Synchronous pulses411 are used in order to make the single power source deliver charge to each of a plurality of coils at timings that bear a fixed relationship to one another. Examples may include simultaneous (414) pulses, and non-simultaneous (415) pulses. SingleSource Asynchronous pulses412 describe those in which charge from a single charge storage device is metered to a plurality of coils in a manner such that each coil fires based upon a signal other than a time scale shared by the coils. The initiation of asynchronous firing may in include, for example, sensing that a series of pulses delivered by one coil has finished. SingleSource Independent pulses413 describe those in which the activity of one coil is not synchronized with, and does not influence the activity of another coil. Very large stored charge reservoirs are required to successfully use this approach.

Multiple Source methods (420) may also be subdivided into categories. MultipleSource Synchronous pulses421 are used in order to make the single power source deliver charge to each of a plurality of coils at timings that bear a fixed relationship to one another. Examples may include simultaneous (424) pulses, and non-simultaneous (425) pulses. MultipleSource Asynchronous pulses422 describe those in which charge from a single charge storage device is metered to a plurality of coils in a manner such that each coil fires based upon a signal other than a time scale shared by the coils. The initiation of asynchronous firing may in include, for example, sensing that a series of pulses delivered by one coil has finished. MultipleSource Independent pulses423 describe those in which the activity of one coil is not synchronized with, and does not influence the activity of another coil. This may be more readily accomplished than with a single source, as power may be specifically allotted to the activity of any given coil.

FIG. 5 shows an array of 3 (double) stimulator coils (referred to herein as three ‘electromagnets’) around a patient's head, in an image based in part on image data from Voxel-Man 3D Navigator. The head of the subject505 is shown transected byplane510. V-shaped double coil520 (also designated as coil A or electromagnet A) is composed of

circular coils

521 and522, and bent at the center where the return path of the current in both coils is in the same direction. Similarly, V-shaped double coil530 (also designated as coil B or electromagnet B) is composed of

circular coils

531 and532 joined at a bent center, and V-shaped double coil540 (also designated as coil C or electromagnet C) is composed of

circular coils

541 and542, joined at a bent center. Within the sub-cortical (or “deep”) target area580 (in this example the left and right cingulum), there is targetedanatomy590, in this example,cingulate fiber bundle580. In another embodiment the electromagnets are not V-shaped, but traditional figure-8 double coils. In still another embodiment, not all of the axes across the faces of the electromagnets are oriented in the same direction.

It is assumed that the distance between the bottom of the nearest cortical sulcus and the underlying deep target is less than the distance between the physical coil centers. Under these conditions, the magnetic fields will summate at the deep target to a greater degree than at the cortical surface.

By pulsing one or more coils at a polarity that is same as that of an adjacent coil, magnetic flux reaching some locations may be augmented. Conversely, by pulsing one or more coils a polarity that is opposite that of an adjacent coil, magnetic flux reaching some locations may be neutralized. For example ifCoil560 is reverse-biased with respect to

coils

550 and570, respectively, the medial aspect of the field emitted by

coils

550 and570 may be largely cancelled. This effect may be controlled by the TMS system described herein, and may be helpful in focusing the target area.

For example, a TMS system as described herein may be used to generate a fast rTMS pulse rate to a peripheral brain region and slow pulse rate to a deep target region. This pattern of stimulation (and the resulting firing pattern and set of instructions for the electromagnet) may be particularly useful for reducing dorsal anterior cingulate metabolic rate while increasing motor cortex or prefrontal metabolic rate, such as in the context of a subject being treated for pain or OCD with depression. When the pulses are rapid but temporally staggered for a time interval that exceeds the chronaxie of the target, a rapid stimulation effect will be registered near each coil, but the target at the intersections of the energy path does not summate because of temporal staggering of the pulses from the periphery. By having some pulses (for example, 1 per second) from the periphery coincide temporally (or occur in rapid succession such that they fall within the chronaxie time of the deep target neurons), a slow rate at the deep target can be achieved even as the sites at the periphery achieve a fast stimulation rate.

In another example, it may be clinically desirable to have a slow rTMS pulse rate to peripheral brain and fast pulse rate to a deep target, at the intersection of the energy paths. For example, it may be desirable to decrease excessive prefrontal metabolism and increase dorsal anterior cingulate activity, for treating attention deficit hyperactivity disorder. The controller may receive the target information (identifying the location of the targets relative to the electromagnets), and may calculate, either before stimulation or on-the-fly, during stimulation, to achieve the desired effect. For example, pulses from each of the multiple sources may be delivered in a staggered fashion so as to make pulses in the periphery slow, and pulses at the intersection of the energy fast. By powering pulses at a rapid rate, but sub-threshold in power (e.g. 99% MT), interspersed with slow rate pulses of suprathreshold power (e.g. 120% MT), the target at the intersection of the energy paths center will experience rapid stimulation, while the locations beneath one or more coils will experience only slow-rate stimulation. Because rTMS pulses are quite brief (approx 0.1 to 0.3 ms in duration), there is an abundance of temporal “space” in between pulses of even a rapid train in which to deliver pulses in an asynchronous fashion, distributed between several different coils.

FIG. 6 shows a table illustrating three example of activation of electromagnets of a TMS system similar to that shown inFIG. 5, in order to achieve a desired effect, including three threshold-based (action-potential-elicited versus no-action-potential-elicited) calculations. In this table, the value of “1” means that an action potential is elicited, as the critical threshold has been exceeded. By contrast, “0” means that no action potential has occurred, as the critical threshold value of the cumulative effect has not been exceeded. T1 through T10 are sample times within an interval, which in this case are defined as 0.1 ms intervals. In alternative embodiments, T1-T10 may represent different time periods. They may or may not be spaced at regular time intervals. In each of the three tables, it is assumed that the distance between the bottom of the nearest cortical sulcus and the underlying deep target is less than the distance between the physical coil centers. Under these conditions, the magnetic fields will summate at the deep target to a greater degree than at the cortical surface. The assumptions behind what produces an adequate summation in each of these scenarios will be further explored below in the discussion ofFIG. 8. Control logic (e.g., part of a controller) may be used to determine (e.g., calculate) this stimulation pattern, as well as the parameters of each stimulation provided by the individual electromagnets, including the powering of each electromagnet, necessary to achieve this stimulation pattern.

In the first of the three tables shown inFIG. 6, the top table shows a scenario in which pulses are delivered from each of Coil A, Coil B, and Coil C at each of the ten time intervals. Accordingly, the summated “mutual deep target” is stimulated to action potential at each pulse, for a net deep stimulation rate of 10 Hz. In this example, the deep target region (at the intersection of the pulses emitted by Coils A, B, and C) is stimulated, as is the more superficial cortical regions beneath Coils A, B and C.

In the second of the three tables shown inFIG. 6, Coils A and B are shown being pulsed at a fast 10 Hz rate, while Coil C is pulsed a slow 1 Hz rate, with a pulse only at T1. Because it is assumed that two coils at these spacing are too far from the mutual deep target to produce summation, the output at the mutual deep target is shown to be a “1”, or action potential only at T1. Thus the net effect at the mutual deep target is 1 Hz stimulation, while the more superficial regions are stimulated at 10 Hz.

In the final of the three tables shown inFIG. 6, Coils A and B are shown being pulsed at a fast 10 Hz rate, while Coil C is pulsed a medium rate of 5 Hz, occurring at every other time interval. Because it is assumed that two coils at these spacing are too far from the mutual deep target to produce summation, the output at the mutual deep target is shown to be a “1”, or action potential only at every other time interval. Thus the net effect at the mutual deep target is 5 Hz stimulation.

Of course, inFIG. 6, the stimulation at each of the cortical regions is indicated as “100% MT” (above threshold) for stimulation at those regions. “MT” refers to motor threshold, a standard (based on stimulation of motor cortex) for evoking a response via Transcranial Magnetic Stimulation; “100% MT” or greater (e.g., “115% MT”) may result in an evoked action potential. The stimulation applied may be below threshold (<100% MT), while still summing to provide sufficient (at or above 100% MT) for the deeper brain regions. Thus, the cortical or regions superficial to the deep target may be un-stimulated so that they do not fire action potentials, while still stimulating the deeper region(s).

FIGS. 7A and 7B shows two different exemplary array configurations, each consisting of four double coils around a patient's head, and centered upon the same cingulate target illustrated as the mutual deep target inFIG. 5. The electromagnets may be movable during the TMS treatment, so that the position of the applied energy may be moved. Such a coil-moving device may be like that described in Schneider and Mishelevich, U.S. patent application Ser. No. 10/821,807. In other example, the TMS system may include stationary coil arrays. Stationary coils may be moved (repositioned) prior to treatment, or between treatment steps.

InFIG. 7A, the upper portion of the figure, coils705,710,715 and720 are in locations too distant from the dorsalanterior cingulate target700 to effectively modulate its activity. However, by moving coils into a closer pattern as shown in the lower figure,FIG. 7B, effective use of the array becomes possible. InFIG. 7B, coils755,760,770 and780 have moved much closer together and closer to dorsalanterior cingulate target750 in a 3D pattern overlaid upon a 2D axial slice. This configuration may also be achieved using three or more standard flat TMS coils, with their “flat planes” at right angles to one another, as described by the present inventors in U.S. patent application Ser. No. 11/429,504.

FIG. 8 is a table that tallies (simulates) the effect of different pulse patterns of the coils shown inFIG. 7B in a manner that considers distance from each coil, and the strength of the magnetic pulses (measured continuously rather than as a binary variable), and the resultant effect upon the target structure relative to interposed superficial structures. The distance to the target for a given electromagnet is DTDT which is the “Distance to The Deep Target” in centimeters measured from the bottom of the cortical sulcus through which the magnetic field from that electromagnet passes. The falloff factor (FF) is an index that reflects what percent of an energy source is present after having traveled 1 cm from its previous position. The % of power at each time period (Tn) reflects the energy applied to the coil (duration and power)? As shown, at the Mutual Deep Target (which is the target at the intersection of the plurality of the stimulation provided by the electromagnets), the percent power is 115%, which is suprathreshold. In the case of 70 mm double coils that may be used for TMS, this factor is approximately 0.50 (fifty percent). Percent power at Mutual Deep Target is the percent of target activation threshold or percent motor threshold. As previously designated, Tn (e.g., T1, T2 . . . Tn) is an arbitrary time: these times may be equally spaced, but are not necessarily so. Percent power shown at Mutual Deep Target may be calculated at each Tn as:

Percent Power at MDT=(FF^DTDT×% Power atT_n)_{Coil A}+(FF^DTDT×% Power atT_n)_{Coil B}+(FF^DTDT×% Power atT_n)_{Coil C}+(FF^DTDT×% Power atT_n)_{Coil D}

Because the cingulate is a bilateral structure that happens to be close to the midline, such distances may be used for both the right and left cingulate structures if target is assumed to be (for the sake of easy calculate) a point between to two cingulate bundles. In the specific scenario illustrated with the particular values shown in the table, it is illustrated that two coils in which the underlying sulci are 2.5 cm from the target plus two coils in which the underlying sulci are 0.5 cm from the target, only 65% power is required from each coil to produce 115% of motor threshold at the target. Of course many other power/distance requirements may be determined with the method shown in this figure. A variant of the method illustrated by this table may be used to separately calculate the effect upon only one target at a time, based upon the distance of that target from each of the energy sources.

As mentioned above, any of the Transcranial Magnetic Stimulation (TMS) systems described herein are typically configured so that each electromagnet is individually controlled or instructed. Thus, these systems may include a controller that specifically coordinates each individual electromagnet, and the individual electromagnets are configured to be capable of acting independently of the others, so that each electromagnet may execute a separate stimulation protocol from the other electromagnets. The controller, which may be a separate component or an integrated component in the system, and may include both hardware and software (or firmware), typically executes a stimulation strategy that includes instructions for the control of each electromagnet. These instructions may include controlling the position, frequency or rate of firing, strength of firing, duration of firing, shape of applied voltage/current (e.g., waveform shape), position (e.g., angle and/or distance from patient, orientation around the patient, and in some variations, movement of the electromagnet), and direction of electromagnetic field. The instructions for controlling stimulation executed by the controller may also be referred to as a treatment plan or treatment strategy. In addition to controlling the activity of each electromagnet, the treatment strategy may also include a stimulation pattern, indicating the pattern of firing of individual electromagnets. As used herein “individual” electromagnets may include sets (e.g. pairs, etc.) of electromagnets.

In some variations the controller also includes logic (hardware and/or software) for generating the treatment strategy. Alternatively, a separate module or component for calculating the treatment strategy may be used. For example, scheduling logic may be used to generate one or more treatment strategies.FIG. 9 is a flowchart illustrating one method of generating a treatment strategy. In general, this treatment strategy is formulated by first determining (or inputting, e.g., by user input) the treatment objectives for each target region, as well as any other regions that may be affected by activation of the electromagnets, such as the brain regions between the electromagnet and the target.

Referring toFIG. 9, the first step in controlling a TMS system such as the systems described herein includes determining the deep brain tissue target(s) to be stimulated1001. Any appropriate target may be chosen. The deep brain region target (e.g. sub-cortical target) may be chosen based on the treatment effect desired (e.g., treatment of depression, etc.). The target deep region of the subject's brain chosen may be provided to the controller (or other module) of the system by numeric (e.g., providing coordinates), by graphical (e.g., indicating on a subject's brain scan), or any other appropriate means. For example, the system may include brain scanning or mapping, or may receive input from brain scanning or mapping. For example, the system may receive the position or coordinates of the target(s) relative to the positions of the electromagnets. Once the primary target(s) (e.g., deep brain targets) have been determined, the system may determine what secondary targets may be affected by the stimulation of the target regions. A secondary target may also be called an incidental target or a collateral target, because, although it is not an intended target, it may be stimulated during the attempt to stimulate the intended target. For example, the cortical region between the deep brain region and the electromagnet, along the pathway of the pulse emitted by the electromagnet, may be considered a secondary or collateral target. In some cases, a collateral target may also be a primary target.

The position of the electromagnets (coils) around the subject may also be adjusted. For example, once the target deep brain region(s) have been selected, the coils around the subject heads may be moved to better reach them. In some variations, the magnets may be continuously moved (e.g., rotated, tilted, or otherwise repositioned) to reach the target region(s). The movement may be coordinated or controlled by the controller, and may be made either at the start of a treatment, or it may occur continuously or periodically during the treatment. Thus the treatment strategy may include control of magnet position and/or movement.

Once the primary target regions and collateral or secondary target regions have been identified, the system may then determine objectives for the primary andsecondary targets1003. The objective may be input from the user (e.g., doctor, technician, etc.) and/or may be selected form a database of objectives. In some variations, the objective for a particular region (e.g., target region) may be expressed as a level of stimulation desired, such as stimulation at a set frequency or range of frequencies (e.g., 5 Hz, 50 Hz, 100 Hz, 200 Hz, 500 Hz, etc.) or a predetermined pattern (e.g., bursts of pulses separated by a delay period). In some variations, the objectives may be broadly characterized as “up regulation”, “down regulation” or “non-stimulation.”For example, an objective of non-stimulation may be interpreted as limiting the target region (e.g., a collateral target region) so that threshold stimulation from the electromagnet (e.g., stimulation less than 100% MT for that region) is not achieved. Thus, although pulses may pass through the target region, they should not achieve 100% MT in that region. Similarly, an objective of “up-regulation” in a particular region may mean stimulation at a frequency of about 5 Hz or greater within the target region. Similarly, an objective of “down-regulation” of a target region may refer to stimulation at a rate of 1 Hz or less. An inventory or database of stimulation objectives for multiple different brain regions may be used (and may be included as part of the system) to provide an adjustable default or pre-set to the system. For example, the adjustable default for collateral targets may be non-stimulation.

Once targets and target objectives have been selected, the system may then apply a method to determine a stimulation strategy. One variation of such a method is shown inFIG. 9, steps1005-1019. For example, the system may generate a plurality of candidate strategies1005 (e.g., m candidate strategies) by applying the target strategies, then score these strategies after simulating their application, and apply the highest-scoring treatment strategy.

FIG. 11 provides one illustration of a method for choosing parameters for candidate strategies, as indicated in

steps

1005 and1007. In general, the step of choosing parameters for each magnet during a treatment strategy may include generating a stimulation pattern wherein the timing of firing of each magnet in the system is coordinated. This stimulation pattern may be fixed, random or mixed, as described above. Further, the firing characteristics of each electromagnet during the stimulation pattern may be selected, including strength, duration, shape of the applied waveform, position of the electromagnet, direction of the field, etc. These parameters (the stimulation pattern and the firing characteristics) may be constrained by the target and target objectives. For example,FIG. 11, steps2001-2027, describes one variation of a method of determining generating a target number of candidate stimulation strategies. For example, permutations of strength, duration, rate, field orientation, etc. may be determined2005 for different permutations ofstimulation patterns2003, and simulated2015 to determine if they achieve thetarget objectives2017 for both primary and collateral targets. This process can be iteratively repeated until an array of candidate strategies (or a best candidate strategy, if they are being scored and compared during this process) is identified. In some variations, pre-set or historical treatment strategies may be applied or used as a starting point for determining a candidate treatment strategy. For example, a database of treatment strategies for particular targets may be used. Thus, in some variations, the system may include such a database, and may add to or modify this database.

Simulation of a candidate treatment plan (e.g., during determination of a treatment plan, as shown inFIG. 11, or during scoring of a treatment plan, as shown inFIG. 9, may be based on the application of the summation (both temporal and spatial) of the applied pulse(s) within each target region. For example, as indicated byFIG. 8, described above, a matrix of simulated stimulation values may be generated to determine what the rate and level of stimulation is for each target region, which can then be compared against the objectives for that target region. Thus, the simulation may apply the attenuation factor, based on the location of the target region relative to the electromagnets. In some variations, particular characteristics of the tissue may also be applied (e.g., region attenuation factors, regional thresholds for stimulation, the effect of field orientations in certain regions, etc.).

FIG. 10 is an adaptation of a figure from the Talairach Atlas in which distances are measured from the bottom of a cortical sulci to a deep target, in this case the cingulate bundle.Brain901 includes gyrus902 (a representative example), sulci903 (a representative example), andlongitudinal fissure904.Sulci903 andlongitudinal fissure904 are typically filled with clear cerebrospinal fluid (not illustrated). Cerebrospinal fluid is composed principally of water with sodium chloride salt, which makes these spaces highly electrically conductive. Insidebrain901 is also the cingulum: principally gray matter but also containingcingulate bundle910, which is composed of axons, or white matter. The distances between the deep target (e.g., cingulate bundle911) and the bottom of two nearby highly conductive sulci are relatively short:distance911 anddistance920.Distance911 anddistance920, when represented in centimeters, may be used within the context of the table inFIG. 8 as DTDT (distance to deep target) numbers. Because the cingulate is a bilateral structure that happens to be close to the midline, such distances may be used for both the right and left cingulate structures if target is assumed to be a point between to two cingulate bundles.

In accordance with the method described, even though there may be radical difference in way the different sources (e.g. coils) behave, the net results at various locations may still be predicted and controlled. Fast and slow stimulation rates may be simultaneously applied to neural tissue on the periphery, while either fast or slow stimulation is being applied to the shared deep target. While the examples of electromagnets shown in the figures are V-shaped double TMS coils, the present method is intended to be generic to any neurostimulation energy source, including, but not limited to standard (flat) double TMS coils or circular TMS coils. The method is also intended to generically apply to neurostimulation energy sources including but not limited to direct or alternating current electrodes, optical neurostimulation light sources, and ultrasound emitters, any of which may be either implanted, externally placed, or within natural orifices.

The various embodiments described above are provided by way of illustration only and should not be construed to limit the invention. Based on the above discussion and illustrations, those skilled in the art will readily recognize that various modifications and changes may be made to the present invention without strictly following the exemplary embodiments and applications illustrated and described herein. Such modifications and changes do not depart from the true spirit and scope of the present invention, which is set forth in the following claims.

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