Dry electrodes for electroencephalography

Abstract

An electroencephalography (EEG) system includes a dry electrode design having a jagged, angular, comb, etc. shaped support housing. Each dry electrode housing includes multiple electrodes where each electrode has multiple contacts for scalp placement with minimal interference from hair. Signals from individual contacts may be disregarded and each housing may provide one or more aggregated signals for data analysis. Each electrode may be placed in close proximity with neighboring electrodes as no conductive gel is required and may be attached to the scalp using straps, elastic cap, spring-type materials, tape, etc. The dry electrode design effectively measures bio-signals including neurological activity.

Description

RELATED APPLICATIONS

This patent is related to U.S. patent application Ser. No. 12/056,190; U.S. patent application Ser. No. 12/056,211; U.S. patent application Ser. No. 12/056,221; U.S. patent application Ser. No. 12/056,225; U.S. patent application Ser. No. 12/113,863; U.S. patent application Ser. No. 12/113,870; U.S. patent application Ser. No. 12/122,240; U.S. patent application Ser. No. 12/122,253; U.S. patent application Ser. No. 12/122,262; U.S. patent application Ser. No. 12/135,066; U.S. patent application Ser. No. 12/135,074; U.S. patent application Ser. No. 12/182,851; U.S. patent application Ser. No. 12/182,874; U.S. patent application Ser. No. 12/199,557; U.S. patent application Ser. No. 12/199,583; U.S. patent application Ser. No. 12/199,596; U.S. patent application Ser. No. 12/200,813; U.S. patent application Ser. No. 12/234,372; U.S. patent application Ser. No. 12/135,069; U.S. patent application Ser. No. 12/234,388; U.S. patent application Ser. No. 12/544,921; U.S. patent application Ser. No. 12/544,934; U.S. patent application Ser. No. 12/544,958; U.S. patent application Ser. No. 12/846,242; U.S. patent application Ser. No. 12/410,380; U.S. patent application Ser. No. 12/410,372; U.S. patent application Ser. No. 12/413,297; U.S. patent application Ser. No. 12/545,455; U.S. patent application Ser. No. 12/608,660; U.S. patent application Ser. No. 12/608,685; U.S. patent application Ser. No. 13/444,149; U.S. patent application Ser. No. 12/608,696; U.S. patent application Ser. No. 12/731,868; U.S. patent application Ser. No. 13/045,457; U.S. patent application Ser. No. 12/778,810; U.S. patent application Ser. No. 12/778,828; U.S. patent application Ser. No. 13/104,821; U.S. patent application Ser. No. 13/104,840; U.S. patent application Ser. No. 12/853,197; U.S. patent application Ser. No. 12/884,034; U.S. patent application Ser. No. 12/868,531; U.S. patent application Ser. No. 12/913,102; U.S. patent application Ser. No. 12/853,213; and U.S. patent application Ser. No. 13/105,774.

TECHNICAL FIELD

The present disclosure relates to electrodes for electroencephalography (EEG).

DESCRIPTION OF RELATED ART

Conventional EEG systems use scalp level electrode attachment to monitor neurological activity. Conductive gels and pastes are often applied before placement of the scalp electrodes to improve sensitivity. However, application of conductive gels and pastes is often inconvenient and time consuming. Furthermore, conductive gels and pastes can often bleed between neighboring electrodes and cause signal contamination.

Some efforts have been made in the development of dry electrodes. However, available dry electrodes have a variety of limitations. Consequently, it is desirable to provide improved dry electrodes for EEG.

BRIEF DESCRIPTION OF THE DRAWINGS

The disclosure may best be understood by reference to the following description taken in conjunction with the accompanying drawings, which illustrate particular example embodiments.

FIGS. 1A-1B illustrate examples of EEG caps.

FIG. 2 illustrates one example of an EEG electrode.

FIG. 3 illustrates one example of an EEG electrode contact.

FIGS. 4A-4B illustrate examples of techniques for selecting an electrode signal.

FIG. 5 illustrates one technique for selecting a local signal.

FIG. 6 illustrates one example of a system for performing distributed neuro-response data collection and analysis.

FIG. 7 illustrates one example of a system that can be used to implement one or more mechanisms.

DESCRIPTION OF PARTICULAR EMBODIMENTS

Reference will now be made in detail to some specific examples of the invention including the best modes contemplated by the inventors for carrying out the invention. Examples of these specific embodiments are illustrated in the accompanying drawings. While the invention is described in conjunction with these specific embodiments, it will be understood that it is not intended to limit the invention to the described embodiments. On the contrary, it is intended to cover alternatives, modifications, and equivalents as may be included within the spirit and scope of the invention as defined by the appended claims.

For example, the techniques and mechanisms of the present invention will be described in the context of particular types of sensor materials. However, it should be noted that the techniques and mechanisms of the present invention apply to a variety of different types of materials. It should be noted that various mechanisms and techniques can be applied to any type of stimuli. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present invention. Particular example embodiments of the present invention may be implemented without some or all of these specific details. In other instances, well known process operations have not been described in detail in order not to unnecessarily obscure the present invention.

Various techniques and mechanisms of the present invention will sometimes be described in singular form for clarity. However, it should be noted that some embodiments include multiple iterations of a technique or multiple instantiations of a mechanism unless noted otherwise. For example, a system uses a processor in a variety of contexts. However, it will be appreciated that a system can use multiple processors while remaining within the scope of the present invention unless otherwise noted. Furthermore, the techniques and mechanisms of the present invention will sometimes describe a connection between two entities. It should be noted that a connection between two entities does not necessarily mean a direct, unimpeded connection, as a variety of other entities may reside between the two entities. For example, a processor may be connected to memory, but it will be appreciated that a variety of bridges and controllers may reside between the processor and memory. Consequently, a connection does not necessarily mean a direct, unimpeded connection unless otherwise noted.

Overview

An electroencephalography (EEG) system includes a dry electrode design having a jagged, angular, comb, etc. shaped support housing. Each dry electrode housing includes multiple electrodes where each electrode has multiple contacts for scalp placement with minimal interference from hair. Signals from individual contacts may be disregarded and each housing may provide one or more aggregated signals for data analysis. Each electrode may be placed in close proximity with neighboring electrodes as no conductive gel is required and may be attached to the scalp using straps, elastic cap, spring-type materials, tape, etc. The dry electrode design effectively measures bio-signals including neurological activity.

Example Embodiments

EEG measures electrical activity associated with post synaptic currents occurring in the milliseconds range. Subcranial EEG can measure electrical activity with the most accuracy, as the bone and dermal layers weaken transmission of a wide range of frequencies. Nonetheless, surface EEG provides a wealth of electrophysiological information if analyzed properly.

Conventional EEG systems use wet electrodes that require skin preparation and application of conductive gels. An example of wet electrodes are silver/silver chloride (Ag/AgCl) electrodes. Silver/silver chloride (Ag/AgCl) electrodes have been widely used because of their low cost and stability, but are often inconvenient and uncomfortable. They require conductive gels that can cause allergic reactions and are typically impractical for use outside of controlled environments. Conductive gels are also ineffectiveness where long recording times are required, as gels dry out and lose efficacy over time. Furthermore, wet electrodes often require significant physical separation from neighboring electrodes because conductive gels can bleed onto neighboring electrodes. This limits the resolution EEG scalp measurements as a limited number of electrodes and associated contacts can be used.

Consequently, some efforts have been made in developing dry electrodes. Dry electrodes can have either a conductive or insulating contact material and are often referred to as dry active electrodes. In particular embodiments, a capacitive coupling between the scalp and the electrode is created so that the signal is transferred to the electrode by a capacitive conduction mechanism. Dry electrode sensor material may be an inert metal like stainless steel or gold. Alternatively, the dry electrode sensor material may be an insulator.

Dry electrodes, however, have significantly higher skin electrode impedance. For dry electrodes to be effective, the techniques and mechanisms of the present invention contemplate mechanisms for compensating for the high impedance. Impedance may vary and/or fluctuate in regions having a significant number of hair follicles. Impedance may also change in region having high skin elasticity. To compensate for variable and/or flucating impedance, the techniques and mechanisms of the present invention provide a jagged shaped support structure for each electrode. Each electrode is provided with multiple contact points or contact pads. In particular embodiments, each electrode selects a locally optimal or preferred signal from the different signals received from the multiple contacts. In some examples, the preferred signal may be a signal having the most consistent and/or highest amplitude during a set of calibrations. According to various embodiments, the locally optimal or preferred signal is amplified and sent to a transmitter. A system also may select a regionally preferred signal from a group of electrodes. According to various embodiments, regionally optimal signals are selected from a group locally optimal signals.

Each electrode may be fabricated using semiconductor manufacturing processes to provide individual electrode integrated circuits. According to various embodiments, each contact has a diameter of 0.5 mm-6 mm. In particular embodiments, each contact has a width of 0.5 mm and a length of 2 mm and a thickness of 2 mm. Smaller contacts more easily navigate through hair to reach the scalp surface. However, too small a contact leads to irritation, and a small contact still does not guarantee that it will reach the scalp. Larger contacts are more comfortable and can provide more surface area for measurement, but can be limited in their ability to read a uniform signal. A large surface contact can not measure a consistent signal due to hair and motion that decouples the contact from the skin surface.

According to various embodiments, each contact is coated with a material to allow for easy navigation through hair while also resisting corrosion. In particular embodiments, each contact is coated with one or more 50 nm-250 nm layers of titanium oxide (TiO₂). TiO₂ is inert on most physiologic media and effectively resists corrosion. In other examples, silicon nitride (Si₃N₄) can also be used. Each contact may be connected to selection circuitry to allow an electrode, or a system, to select one or more preferred signals of the electrode. In some instances, no signal may be suitable. Individual electrode may also include filters, capacitors, diodes, power supplies, and amplifiers, and transmitters.

The EEG electrodes can be used to measure spontaneous EEG. The bandwidth of the measurement can range from 0.05 Hz to 80 Hz. The amplitude of the EEG signal can range from 50 uV-250 uV with sensitivity of 10 uV/mm. Evoked potentials (EP) are time-locked averages of neurological activity. According to various embodiments, EP amplitudes range from 0.05-30 uV. It is recognized that both wet and dry electrodes can be used to efficiently measure a variety of signals resulting from neurological activity including spontaneous EEG and EP. According to various embodiments, portable EEG with dry electrodes provide a large amount of neuro-response information.

FIGS. 1A-1B illustrate particular examples of mechanisms for placing EEG dry electrodes on a surface such as the scalp of a subject. According to various embodiments, the distributed neuro-response data collection mechanism includes multiple EEG dry electrodes including electrodes 111, 113, and 115. In particular embodiments, the EEG dry electrodes are spring loaded or cushion loaded operate to detect neurological activity with minimal interference from hair. The EEG dry electrodes also do not require use of any electrically conductive gels. The EEG dry electrodes may each be configured on a longitudinal or latitudinal zig zag arrangement. Each arrangement may have multiple EEG dry electrodes. Each EEG dry electrode may have multiple contacts. According to various embodiments, distributed neuro-response data collection mechanism also includes EOG sensors such as sensor 121 used to detect eye movements.

The data collection mechanism may also include a transmitter and/or receiver to send collected neuro-response data to a data analysis system. In some examples, a transceiver 141 transmits all collected media such as video and/or audio, neuro-response, and sensor data to a data analyzer. In other examples, a transceiver 141 transmits only interested data provided by a filter 143. In other examples, the transceiver 141 also receives information that can be provided to a user or used to modify a system. The filter 143 can remove noise as well as uninteresting portions of collected data. The filter 143 can significantly reduce network usage and can be valuable when limited network resources are available. In some examples, the transceiver can be connected to a computer system that then transmits data over a wide area network to a data analyzer. In other examples, the transceiver sends data over a wide area network to a data analyzer. Other components such as fMRI and MEG that are not yet portable but may become portable at some point may also be integrated into a headset, cap, band, clips, etc.

The headset, cap, band, clips, comb, etc., may be configured in a very discrete manner. It should be noted that some components of a neuro-response data collection mechanism have not been shown for clarity. For example, a battery may be required to power components such as cameras and sensors and wiring from the battery are not shown. Similarly, a transceiver may include an antenna that is similarly not shown for clarity purposes.

In some examples a comb type distributed neuro-response data collection mechanism includes multiple EEG dry electrodes as shown in FIG. 1B. In the illustrated example, the comb structure includes four extensions. Each of the extensions has a respective radius of curvature. As shown in FIG. 1B, the respective radii of curvature are substantially the same. The comb structure also includes electrodes 161, 163, and 165. In particular embodiments, the EEG dry electrodes operate to detect neurological activity with minimal interference from hair. The EEG dry electrodes also do not require use of any electrically conductive gels. According to various embodiments, distributed neuro-response data collection mechanism also includes EOG sensors such as sensor 171 used to detect eye movements.

The data collection mechanism may also include a transmitter and/or receiver to send collected neuro-response data to a data analysis system. In some examples, a transceiver 191 transmits all collected media such as video and/or audio, neuro-response, and sensor data to a data analyzer. In other examples, a transceiver 191 transmits only interested data provided by a filter 193. In other examples, the transceiver 191 also receives information that can be provided to a user or used to modify a system. The filter 193 can remove noise as well as uninteresting portions of collected data. The filter 193 can significantly reduce network usage and can be valuable when limited network resources are available. In some examples, the transceiver can be connected to a computer system that then transmits data over a wide area network to a data analyzer. In other examples, the transceiver sends data over a wide area network to a data analyzer. Other components such as fMRI and MEG that are not yet portable but may become portable at some point may also be integrated into a headset, cap, band, clips, etc.

FIG. 2 illustrates one example of an electrode having multiple contacts and/or sensors. According to various embodiments, each contact 201, 203, 205, and 207 has a diameter of 0.05 mm-6 mm. In particular embodiments, each contact is cylindrical and has a spherical tip. In other examples, each contact or sensor has a rectangular cross section and a conical tip. Other cross sections and structures are possible. Smaller contacts more easily navigate through hair to reach the scalp surface. However, too small a contact leads to irritation, and a small contact still does not guarantee contact with the scalp.

Shielding is provided to reduce electromagnetic interference on electrode circuitry. According to various embodiments, selection circuitry 211 is provided to select the electrode having the highest signal quality. In some examples, hair follicles may prevent firm contact between particular sensors 201, 203, 205, and 207 and the scalp. In particular embodiments, selection circuitry 211 identifies the sensor providing the signal with the highest average amplitude. In other examples, selection circuitry 211 identifies the sensor providing the signal closest to the expected signal. In other examples, selection circuitry may not be provided and local selection of a sensor signal for a particular electrode may be performed by an EEG system after transmission of all signals to the EEG system.

According to various embodiments, a preamplifier 223 may be provided before or after selection circuitry to strengthen a signal detected by contacts 201, 203, 205, and/or 207. According to various embodiments, the pre-amplifier gain can be set to 2-50 kv/V for use with dry electrodes. Power source 221 may be a battery, a radio frequency power source, a piezo-electric power source, etc. In particular embodiments, a filter 231 may be a simple low pass, high pass, or band pass filter used to remove signals falling outside of the detectable EEG signal frequency ranges. In other examples, the filter can be used to remove known artifacts generated by movements such as jaw movements or blinking.

Transmitter 233 sends detected signals to an EEG system. In some examples, the transmitter 233 is a wired or wireless transceiver that digitizes signals and transmits them to a computing system after amplification and filtering. Wired systems may require extensive shielding particularly if the EEG electrodes are used in conjunction with other systems such as fMRI.

FIG. 3 illustrates one example of a group of electrodes having multiple contacts and/or sensors. According to various embodiments, each electrode 301, 321, and 341 includes corresponding skin and/or scalp contacts. Electrode 301 includes contacts 303, 305, and 307. Electrode 321 includes contacts 323, 325, and 327. Electrode 341 includes contacts 343, 345, and 347.

According to various embodiments, each contact has a size ranging from 0.1 mm-5 mm. In particular embodiments, each contact is cylindrical and has a spherical tip. In other examples, each contact or sensor has a rectangular cross section and a rectangular tip. A variety of configurations are possible. Smaller contacts more easily navigate through hair to reach the scalp surface. However, too small a contact leads to irritation, and a small contact still does not guarantee that it will reach the scalp.

Shielding is provided to reduce electromagnetic interference on electrode circuitry. According to various embodiments, each electrode 301, 321, and 341 includes corresponding selection circuitry 309, 329, and 349. In particular embodiments, selection circuitry 309, 329, and 349 identify locally preferred signals. In some examples, signals having good signal to noise characteristics are selected by selection circuitry 309, 329, and 349 at each electrode. In other examples, selection circuitry 309, 329, and 349 identify one or more signals providing the signal closest to the expected signal. In other examples, selection circuitry may not be provided and local selection of a sensor signal for a particular electrode may be performed by regional signal selection circuitry 363. According to various embodiments, selection circuitry 309, 329, and 349 select locally preferred signals while regional signal selection circuitry 363 select regionally preferred signals from a group of electrodes such as electrodes 301, 321, and 341.

According to various embodiments, amplifiers and/or preamplifiers 313, 333, and 353 may be provided before or after selection circuitry to strengthen a signal detected by contacts 303, 305, 307, 323, 325, 327, and 343, 345, and 347. According to various embodiments, the pre-amplifier gain can be set to 2-50 kv/V for use with dry electrodes. Power sources 311, 331, and 351 may be batteries, radio frequency power sources, piezo-electric power sources, etc. In particular embodiments, filters may also be provided. Filter 315, 335, and 355 may be low pass, high pass, band pass filters, etc., used to remove signals falling outside of the detectable EEG signal frequency ranges. In other examples, the filters can be used to remove known artifacts generated by movements such as jaw movements or blinking.

Transmitters 317, 337, and 357 send detected signals to an EEG system. In some examples, the transmitter 317, 337, and 357 are wired or wireless transceivers that digitize signals and transmit them to a computing system after amplification and filtering. The transceivers may also receive signals from an EEG system to dynamically modify frequency ranges detected or amplifier gains to be applied. Wired systems may require extensive shielding particular if the EEG electrodes are used in conjunction with other systems such as fMRI. According to various embodiments, individual electrodes 301, 321, and 341 are arranged on a jagged structure electrode housing structure 371. According to various embodiments, the jagged structure 371 is a longitudinally or latitudinally arranged zig zag or wave structure configured to displace as much hair as possible as EEG electrodes are placed on the scalp. Zig zag configurations may be horizontally or vertically placed. An EEG system may also include a receiver 361 to obtain signals from individual electrodes 301, 321, and 341. Regional signal selection circuitry 363 selects preferred signals from groups of electrodes. According to various embodiments, hundreds of electrodes and thousands of contacts may be placed on an individual scalp, and the regional signal selection circuitry 363 remove signals from sensors having poor or fluctuating contact with the scalp. In other examples, far fewer or a far greater number of electrodes can be used.

The locally selected and the regionally selected signals are provided to a data analyzer 365. Data analysis may include intra-modality response synthesis and cross-modality response synthesis to enhance effectiveness measures. It should be noted that in some particular instances, one type of synthesis may be performed without performing other types of synthesis. For example, cross-modality response synthesis may be performed with or without intra-modality synthesis.

FIG. 4A illustrates one mechanism for selecting a local signal. At 401, reference signals are obtained. According to various embodiments, reference signals may be ground signals used as a reference point for measured signals. At 403, controlled stimulus materials are provided. In particular embodiments, controlled stimulus materials are materials known to elicit particular neurological responses. In other examples, stimulus materials for analysis are provided. At 405, signals are obtained from multiple contacts associated with an electrode. In particular embodiments, each electrode includes multiple contacts arranged in a tooth shaped support structure to allow effective scalp contact through hair.

According to various embodiments, the worst signals are removed at 407. In particular embodiments, signals showing amplifier blocking characteristics are removed. Anything having a significant amount of high frequency noise, (e.g. >40 Hz) can also be eliminated. In some examples, anything pinning characteristics associated with constant decreasing amplitude are removed as the decrease in amplitude may indicate imminent detachment of the contact from the scalp. In other embodiments, having low signal to noise ratios are disregarded. In still other embodiments, signals having poor drift and jitter characteristics are removed. At 413, remaining contacts are averaged to provide a local signal. In some examples, signals from four remaining contacts are averaged to provide an aggregated signal. A selection, averaging, or other combination of signals is referred to herein as an aggregated signal. In some examples, two signals having good characteristics are averaged to provide an aggregated signal.

FIG. 4B illustrates another mechanism for selecting a local signal. At 451, reference signals are obtained. According to various embodiments, reference signals may be ground signals used as a reference point for measured signals. At 453, controlled stimulus materials are provided. In particular embodiments, controlled stimulus materials are materials known to elicit particular neurological responses. In other examples, stimulus materials for analysis are provided. At 455, signals are obtained from multiple contacts associated with an electrode. In particular embodiments, each electrode includes multiple contacts arranged in a tooth shaped support structure to allow effective scalp contact through hair.

According to various embodiments, local signals with the closest correlation to expected signals are identified at 457. In particular embodiments, signals having the highest average amplitude at determined at 459. Signals having the highest signal to noise ratio may also be identified at 461. At 463, a contact providing the local signal is selected.

FIG. 5 illustrates one mechanism for selecting a local and regional signal. At 501, select local signals are obtained. According to various embodiments, local signals having poor characteristics are removed at 503. In particular embodiments, signals associated with amplifier blocking or pinning are removed. Signals showing characteristics corresponding with imminent detachment of the contact from the scalp may also be removed 505. In other embodiments, signals having low signal to noise ratios are disregarded. At signals having the highest average amplitude may be determined. Signals having the highest signal to noise ratio may also be identified. At 507, regional signals are selected from electrodes in the same electrode housing. According to various embodiments, each electrode housing may include 2-10 electrodes, where each individual electrode includes multiple contacts.

Each electrode housing may be a zigzag, rectangular, cylindrical, comb, etc. type structure arranged to allow electrode contact with the scalp with minimal interference from hair. In particular embodiments, each housing ranges from 0.2 mm to 2 cm in length, 1 mm to 1 cm in width, and 0.2 mm to 2 cm in thickness. In other particular embodiments, each housing ranges from 1 mm to 3 cm in diameter and 1.1 mm to 2 cm in thickness. Configurations may vary widely depending on manufacturing technologies and materials. According to various embodiments, the non-eliminated signals or selected signals are averaged at 509. In some examples, one signal may be selected as the desired signal, although taking remaining selected signals from the housing may allow for further noise reduction. At 511, selected, averaged, and/or aggregated signals from the electrode housing are sent for analysis.

FIG. 6 illustrates one example of neuro-response data collection using dry electrodes. At 601, user information is received from a subject provided with a neuro-response data collection mechanism. According to various embodiments, the subject sends data including age, gender, income, location, interest, ethnicity, etc. after being provided with an EEG cap including EEG electrodes, EOG sensors, cameras, recorders, network interfaces, and a global position system (GPS) device integrated into an unobtrusive device that can be worn during typical activities.

At 603, neuro-response data, video and audio recorded data, timing information, and/or location information, etc., is received from the subject neuro-response data collection mechanism. According to various embodiments, EEG, EOG, pupillary dilation, facial emotion encoding data, video, images, audio, GPS data, timestamps, etc., are transmitted from the subject to a neuro-response data analyzer. In particular embodiments, data is filtered and compressed prior to transmission. For example, only video and audio corresponding to neuro-logically salient events are transmitted to save on network bandwidth. According to various embodiments, neuro-response and associated data is transmitted directly from an EEG cap wide area network interface to a data analyzer. In particular embodiments, neuro-response and associated data is transmitted to a computer system that then performs compression and filtering of the data before transmitting the data to a data analyzer over a network.

According to various embodiments, data is also passed through a data cleanser to remove noise and artifacts that may make data more difficult to interpret. According to various embodiments, the data cleanser removes EEG electrical activity associated with blinking and other endogenous/exogenous artifacts. Data cleansing may be performed before or after data transmission to a data analyzer.

At 605, stimulus material is identified. According to various embodiments, stimulus material is identified based on user input. For example, a user watching a particular movie may enter the title of the movie along with how and where it was viewed. Alternatively, video recording may be analyzed using text, facial, brand, video, image, and audio recognition algorithms to determine what the user was viewing. Eye tracking movements can determine where user attention is focused at any given time. Although that eye movements do occur when attention is diverted, it is recognized that focused attention typically occurs when eye position is focused in the forward direction. Consequently, the EEG cap and video camera direction typically coincide with the direction of user attention. EEG data may also be tagged to indicate correspondence with particular video and audio events. According to various embodiments, a user walking down a supermarket aisle may direct attention to certain products that are identified using video recordings and correlated with neuro-response measures to determine the effectiveness of product labeling.

At 607, neuro-response data is synchronized with timing, location, and other stimulus material data. According to various embodiments, neuro-response data such as EEG and EOG data is tagged to indicate what the subject is viewing or listening to at a particular time.

At 609, data analysis is performed. Data analysis may include intra-modality response synthesis and cross-modality response synthesis to enhance effectiveness measures. It should be noted that in some particular instances, one type of synthesis may be performed without performing other types of synthesis. For example, cross-modality response synthesis may be performed with or without intra-modality synthesis.

A variety of mechanisms can be used to perform data analysis 609. In particular embodiments, a stimulus attributes repository is accessed to obtain attributes and characteristics of the stimulus materials, along with purposes, intents, objectives, etc. In particular embodiments, EEG response data is synthesized to provide an enhanced assessment of effectiveness. According to various embodiments, EEG measures electrical activity resulting from thousands of simultaneous neural processes associated with different portions of the brain. EEG data can be classified in various bands. According to various embodiments, brainwave frequencies include delta, theta, alpha, beta, and gamma frequency ranges. Delta waves are classified as those less than 4 Hz and are prominent during deep sleep. Theta waves have frequencies between 3.5 to 7.5 Hz and are associated with memories, attention, emotions, and sensations. Theta waves are typically prominent during states of internal focus.

Alpha frequencies reside between 7.5 and 13 Hz and typically peak around 10 Hz. Alpha waves are prominent during states of relaxation. Beta waves have a frequency range between 14 and 30 Hz. Beta waves are prominent during states of motor control, long range synchronization between brain areas, analytical problem solving, judgment, and decision making. Gamma waves occur between 30 and 60 Hz and are involved in binding of different populations of neurons together into a network for the purpose of carrying out a certain cognitive or motor function, as well as in attention and memory. Because the skull and dermal layers attenuate waves in this frequency range, brain waves above 75-80 Hz are difficult to detect and are often not used for stimuli response assessment.

However, the techniques and mechanisms of the present invention recognize that analyzing high gamma band (kappa-band: Above 60 Hz) measurements, in addition to theta, alpha, beta, and low gamma band measurements, enhances neurological attention, emotional engagement and retention component estimates. In particular embodiments, EEG measurements including difficult to detect high gamma or kappa band measurements are obtained, enhanced, and evaluated. Subject and task specific signature sub-bands in the theta, alpha, beta, gamma and kappa bands are identified to provide enhanced response estimates. According to various embodiments, high gamma waves (kappa-band) above 80 Hz (typically detectable with sub-cranial EEG and/or magnetoencephalograophy) can be used in inverse model-based enhancement of the frequency responses to the stimuli.

Various embodiments of the present invention recognize that particular sub-bands within each frequency range have particular prominence during certain activities. A subset of the frequencies in a particular band is referred to herein as a sub-band. For example, a sub-band may include the 40-45 Hz range within the gamma band. In particular embodiments, multiple sub-bands within the different bands are selected while remaining frequencies are band pass filtered. In particular embodiments, multiple sub-band responses may be enhanced, while the remaining frequency responses may be attenuated.

An information theory based band-weighting model is used for adaptive extraction of selective dataset specific, subject specific, task specific bands to enhance the effectiveness measure. Adaptive extraction may be performed using fuzzy scaling. Stimuli can be presented and enhanced measurements determined multiple times to determine the variation profiles across multiple presentations. Determining various profiles provides an enhanced assessment of the primary responses as well as the longevity (wear-out) of the marketing and entertainment stimuli. The synchronous response of multiple individuals to stimuli presented in concert is measured to determine an enhanced across subject synchrony measure of effectiveness. According to various embodiments, the synchronous response may be determined for multiple subjects residing in separate locations or for multiple subjects residing in the same location.

Although a variety of synthesis mechanisms are described, it should be recognized that any number of mechanisms can be applied—in sequence or in parallel with or without interaction between the mechanisms.

Although intra-modality synthesis mechanisms provide enhanced significance data, additional cross-modality synthesis mechanisms can also be applied. A variety of mechanisms such as EEG, Eye Tracking, GSR, EOG, and facial emotion encoding are connected to a cross-modality synthesis mechanism. Other mechanisms as well as variations and enhancements on existing mechanisms may also be included. According to various embodiments, data from a specific modality can be enhanced using data from one or more other modalities. In particular embodiments, EEG typically makes frequency measurements in different bands like alpha, beta and gamma to provide estimates of significance. However, the techniques of the present invention recognize that significance measures can be enhanced further using information from other modalities.

For example, facial emotion encoding measures can be used to enhance the valence of the EEG emotional engagement measure. EOG and eye tracking saccadic measures of object entities can be used to enhance the EEG estimates of significance including but not limited to attention, emotional engagement, and memory retention. According to various embodiments, a cross-modality synthesis mechanism performs time and phase shifting of data to allow data from different modalities to align. In some examples, it is recognized that an EEG response will often occur hundreds of milliseconds before a facial emotion measurement changes. Correlations can be drawn and time and phase shifts made on an individual as well as a group basis. In other examples, saccadic eye movements may be determined as occurring before and after particular EEG responses. According to various embodiments, time corrected GSR measures are used to scale and enhance the EEG estimates of significance including attention, emotional engagement and memory retention measures.

Evidence of the occurrence or non-occurrence of specific time domain difference event-related potential components (like the DERP) in specific regions correlates with subject responsiveness to specific stimulus. According to various embodiments, ERP measures are enhanced using EEG time-frequency measures (ERPSP) in response to the presentation of the marketing and entertainment stimuli. Specific portions are extracted and isolated to identify ERP, DERP and ERPSP analyses to perform. In particular embodiments, an EEG frequency estimation of attention, emotion and memory retention (ERPSP) is used as a co-factor in enhancing the ERP, DERP and time-domain response analysis.

EOG measures saccades to determine the presence of attention to specific objects of stimulus. Eye tracking measures the subject's gaze path, location and dwell on specific objects of stimulus. According to various embodiments, EOG and eye tracking is enhanced by measuring the presence of lambda waves (a neurophysiological index of saccade effectiveness) in the ongoing EEG in the occipital and extra striate regions, triggered by the slope of saccade-onset to estimate the significance of the EOG and eye tracking measures. In particular embodiments, specific EEG signatures of activity such as slow potential shifts and measures of coherence in time-frequency responses at the Frontal Eye Field (FEF) regions that preceded saccade-onset are measured to enhance the effectiveness of the saccadic activity data.

According to various embodiments, facial emotion encoding uses templates generated by measuring facial muscle positions and movements of individuals expressing various emotions prior to the testing session. These individual specific facial emotion encoding templates are matched with the individual responses to identify subject emotional response. In particular embodiments, these facial emotion encoding measurements are enhanced by evaluating inter-hemispherical asymmetries in EEG responses in specific frequency bands and measuring frequency band interactions. The techniques of the present invention recognize that not only are particular frequency bands significant in EEG responses, but particular frequency bands used for communication between particular areas of the brain are significant. Consequently, these EEG responses enhance the EMG, graphic and video based facial emotion identification.

Integrated responses are generated at 611. According to various embodiments, the data communication device transmits data to the response integration using protocols such as the File Transfer Protocol (FTP), Hypertext Transfer Protocol (HTTP) along with a variety of conventional, bus, wired network, wireless network, satellite, and proprietary communication protocols. The data transmitted can include the data in its entirety, excerpts of data, converted data, and/or elicited response measures. According to various embodiments, data is sent using a telecommunications, wireless, Internet, satellite, or any other communication mechanisms that is capable of conveying information from multiple subject locations for data integration and analysis. The mechanism may be integrated in a set top box, computer system, receiver, mobile device, etc.

In particular embodiments, the data communication device sends data to the response integration system. According to various embodiments, the response integration system combines analyzed and enhanced responses to the stimulus material while using information about stimulus material attributes. In particular embodiments, the response integration system also collects and integrates user behavioral and survey responses with the analyzed and enhanced response data to more effectively measure and track distributed neuro-responses to stimulus materials. According to various embodiments, the response integration system obtains attributes such as requirements and purposes of the stimulus material presented.

Some of these requirements and purposes may be obtained from a variety of databases. According to various embodiments, the response integration system also includes mechanisms for the collection and storage of demographic, statistical and/or survey based responses to different entertainment, marketing, advertising and other audio/visual/tactile/olfactory material. If this information is stored externally, the response integration system can include a mechanism for the push and/or pull integration of the data, such as querying, extraction, recording, modification, and/or updating.

The response integration system can further include an adaptive learning component that refines user or group profiles and tracks variations in the distributed neuro-response data collection system to particular stimuli or series of stimuli over time. This information can be made available for other purposes, such as use of the information for presentation attribute decision making. According to various embodiments, the response integration system builds and uses responses of users having similar profiles and demographics to provide integrated responses at 611. In particular embodiments, stimulus and response data is stored in a repository at 613 for later retrieval and analysis.

According to various embodiments, various mechanisms such as the data collection mechanisms, the intra-modality synthesis mechanisms, cross-modality synthesis mechanisms, etc. are implemented on multiple devices. However, it is also possible that the various mechanisms be implemented in hardware, firmware, and/or software in a single system. FIG. 7 provides one example of a system that can be used to implement one or more mechanisms. For example, the system shown in FIG. 7 may be used to implement a data analyzer.

According to particular example embodiments, a system 700 suitable for implementing particular embodiments of the present invention includes a processor 701, a memory 703, an interface 711, and a bus 715 (e.g., a PCI bus). When acting under the control of appropriate software or firmware, the processor 701 is responsible for such tasks such as pattern generation. Various specially configured devices can also be used in place of a processor 701 or in addition to processor 701. The complete implementation can also be done in custom hardware. The interface 711 is typically configured to send and receive data packets or data segments over a network. Particular examples of interfaces the device supports include host bus adapter (HBA) interfaces, Ethernet interfaces, frame relay interfaces, cable interfaces, DSL interfaces, token ring interfaces, and the like.

In addition, various very high-speed interfaces may be provided such as fast Ethernet interfaces, Gigabit Ethernet interfaces, ATM interfaces, HSSI interfaces, POS interfaces, FDDI interfaces and the like. Generally, these interfaces may include ports appropriate for communication with the appropriate media. In some cases, they may also include an independent processor and, in some instances, volatile RAM. The independent processors may control such communications intensive tasks as data synthesis.

According to particular example embodiments, the system 700 uses memory 703 to store data, algorithms and program instructions. The program instructions may control the operation of an operating system and/or one or more applications, for example. The memory or memories may also be configured to store received data and process received data.

Because such information and program instructions may be employed to implement the systems/methods described herein, the present invention relates to tangible, machine readable media that include program instructions, state information, etc. for performing various operations described herein. Examples of machine-readable media include, but are not limited to, magnetic media such as hard disks, floppy disks, and magnetic tape; optical media such as CD-ROM disks and DVDs; magneto-optical media such as optical disks; and hardware devices that are specially configured to store and perform program instructions, such as read-only memory devices (ROM) and random access memory (RAM). Examples of program instructions include both machine code, such as produced by a compiler, and files containing higher level code that may be executed by the computer using an interpreter.

Although the foregoing invention has been described in some detail for purposes of clarity of understanding, it will be apparent that certain changes and modifications may be practiced within the scope of the appended claims. Therefore, the present embodiments are to be considered as illustrative and not restrictive and the invention is not to be limited to the details given herein, but may be modified within the scope and equivalents of the appended claims.

Claims

1. An apparatus comprising: a comb having a comb base, a first extension, and a second extension, the first extension and the second extension extending from the comb base, the comb base including a sensor to detect eye movement, the sensor disposed on an end of the comb base;a first electrode carried by the first extension, the first electrode including a first transceiver to receive a first control signal;a first filter communicatively coupled to the first transceiver to automatically dynamically modify a first frequency range of signals to be detected by the first electrode in response to the first control signal;a second electrode carried by the second extension, the second electrode including a second transceiver to receive a second control signal;a second filter communicatively coupled to the second transceiver to automatically dynamically modify a second frequency range of signals to be detected by the second electrode in response to the second control signal;a third electrode carried by the comb base, the third electrode including a third transceiver to receive a third control signal; anda third filter communicatively coupled to the third transceiver to automatically dynamically modify a third frequency range of signals to be detected by the third electrode in response to the third control signal;wherein at least one of the first control signal received by the first transceiver, the second control signal received by the second transceiver, or the third control signal received by the third transceiver is based on at least one of (a) a region of detection of the first electrode, (b) a region of detection of the second electrode, and (c) a region of detection of the third electrode.

2. The apparatus of claim 1, wherein the first extension and the second extension have a non-linear shape.

3. The apparatus of claim 1, wherein the third electrode has a plurality of contacts.

4. The apparatus of claim 3, wherein at least one of the contacts has a rectangular cross-section and a conical tip.

5. The apparatus of claim 1, wherein the first extension has a pointed tip, the first extension including a plurality of electrodes, the first electrode and the plurality of electrodes spaced from the pointed tip.

6. The apparatus of claim 1, wherein the first extension has a first radius of curvature and the second extension has a second radius of curvature substantially the same as the first radius of curvature.

7. The apparatus of claim 1, further including a third extension and a fourth electrode carried by the third extension.

8. The apparatus of claim 7, further including a fifth electrode carried by the first extension, a sixth electrode carried by the second extension, a seventh electrode carried by the third extension, and an eighth electrode carried by the comb base.

9. The apparatus of claim 7, wherein the first extension has a first radius of curvature, the second extension has a second radius of curvature substantially the same as the first radius of curvature, and the third extension has a third radius of curvature substantially the same as the first radius of curvature.

10. The apparatus of claim 9, further including a fifth electrode carried by the first extension, a sixth electrode carried by the second extension, a seventh electrode carried by the third extension, and an eighth electrode carried by the comb base.

11. The apparatus of claim 10, wherein the first electrode on the first extension is spaced from the second extension a first distance, and the fifth electrode on the first extension is spaced from the second extension the first distance.

12. The apparatus of claim 1, wherein the first electrode further includes: a first contact point to gather a first signal from a subject;a second contact point to gather a second signal from the subject;a third contact point to gather a third signal from the subject; anda selector to (1) discard one of the first signal, the second signal or the third signal based on a first characteristic of the first signal, a second characteristic of the second signal and a third characteristic of the third signal, and to (2) combine two of the first signal, the second signal and the third signal to form the first control signal, the two of the first signal, the second signal and the third signal excluding the discarded one of the first signal, the second signal and the third signal.

13. The apparatus of claim 1, wherein the first electrode, the second electrode, and the third electrode are disposed in a zig zag arrangement.

14. The apparatus of claim 1, wherein the first extension and the second extension have tapered ends opposite the comb base.

15. The apparatus of claim 1, wherein each of the first, second, and third electrodes includes a plurality of contacts, the plurality of contacts coated with one or more of a layer of titanium oxide or a layer of silicon nitride to enable navigation through hair of a subject.

16. The apparatus of claim 15, wherein each layer of the one or more layers has a thickness of 50-250 nanometers (nm).

17. An apparatus to gather neurological signals from a surface of a head of a subject, the apparatus comprising: a comb including a comb base, a first extension coupled to the comb base, and a second extension coupled to the comb base, the first extension having a first tapered end opposite the comb base to navigate on the surface of the head through hair, and the second extension having a second tapered end to navigate on the surface of the head through the hair;a sensor disposed on an end of the comb base to detect eye movement;a first electrode carried by the first extension, the first electrode to gather a first neurological signal;a second electrode carried by the first extension, the second electrode to gather a second neurological signal; anda third electrode carried by the comb base, the third electrode to gather a third neurological signal.

18. The apparatus of claim 17, wherein the first electrode includes a plurality of contact points and selection circuitry, the selection circuitry to select data from a first contact point of the plurality of contact points as the first neurological signal.

19. The apparatus of claim 17, further including: a third extension coupled to the comb base, the third extension having a third tapered end opposite the comb base to navigate on the surface through the hair; anda fourth electrode carried by the third extension, the fourth electrode to gather a fourth neurological signal,wherein the first extension has a first radius of curvature, the second extension has a second radius of curvature substantially the same as the first radius of curvature, and the third extension has a third radius of curvature substantially the same as the first radius of curvature.

20. The apparatus of claim 19, wherein the comb base has a fourth radius of curvature different from the first radius of curvature.

21. The apparatus of claim 20, wherein the first extension, second extension, and third extension curve in a first direction, and the comb base curves in a second direction different from the first direction.