The present disclosure relates generally to techniques for designing sensing devices that are implantable in a body of a patient.
Implantable biomedical devices may utilize component microelectronic circuitry implanted in the body of a patient to perform functions benefiting the health of the patient. For example, in the field of neurological monitoring, multiple electrodes may be implanted in diverse locations near, on, or in a patient's brain to monitor cortical potentials (Electro Encephalogram, or EEG). This data may be subsequently processed in order to determine if a patient is experiencing a seizure, or is at elevated susceptibility to experiencing a seizure. See, e.g., U.S. patent application Ser. No. 12/020,450, “Systems and Methods for Identifying a Contra-ictal Condition in a Subject,” filed Jan. 25, 2008, assigned to the assignee of the present application, the contents of which are hereby incorporated by reference in their entirety.
The design of signal conditioning front-end circuitry for implantable biomedical devices calls for robust and accurate signal sensing capabilities that minimize the effects of external environmental signal sources and the effects of unrelated physiological processes, while effecting minimal disturbance to the patient. A number of different amplification approaches may be used to measure neurological potentials. An often used approach involves measuring the difference in potential between two adjacent electrodes. Because the electrodes are nearby each other, they tend to be affected in the same way by interfering sources such as external static potentials, as interfering signals tend to manifest themselves as common to both channels (“common-mode”). By measuring only the difference in potential between the two electrodes (“differential-mode”), common-mode interference signals may be rejected.
A well-designed system will address factors that prevent common-mode signals from being converted into differential-mode signals (said to be an artifact of the interfering signal), which may be quantified by the “Common Mode Rejection Ratio”, or CMRR. Achieving a high CMRR typically requires the use of circuit components with tight tolerances and circuits that embody symmetrical features. While differential measurement approaches tend to provide good rejection of certain types of interfering signals, they also introduce measurement issues. In particular, the ability to resolve the location where a signal is being generated becomes an issue. This is because, in a differential system, it may be unclear as to which of the two electrodes being used in the measurement is sensing the signal.
Other measurement approaches may be used that attempt to measure the signal associated with a single sensing electrode. This is often the case when using implanted sub-dural monitoring electrodes. Use of the signal from a single electrode may help to better localize a region of interest, such as brain tissue that is associated with seizure initiation, i.e., a “seizure onset zone”. The ability to measure the potential associated with a single electrode may also have advantages for use with algorithms such as seizure advisory algorithms. In practice, potentials cannot be measured alone, they must be measured in comparison with another potential. To measure the signal from a single electrode requires the designation of a reference point or reference electrode. A fundamental limitation is that unwanted signal appearing on the reference electrode cannot be distinguished from signal arising on the sensing electrode. For this reason, the reference electrode should be chosen or designed to be as free from signal as possible.
In conventional neuro-amplification systems, a designated reference channel is provided. A user will attempt to place the associated reference electrode in an area that is electrically “quiet,” meaning that the location is largely free from neuro-potentials, myographic potentials, and interfering environmental signals. By its very nature, the reference electrode location tends to be well separated from the area where the desired neuro-potentials are being measured. A typical reference location choice would be the vertex of the patient's head. This location is relatively distant from underlying muscle and associated artifact and tends to exhibit smaller neuro-potential signals. The separation of the reference electrode and the sensing electrodes means that interfering sources may act on the electrodes differently, arising in artifact that is difficult or impossible to remove. When used as part of an implantable system, the separation of the measuring electrodes from the reference electrode could also lead to a need for a more complex system, the need for additional surgical incisions, and increased risk of complications.
It would be desirable to create a neuro-amplification system that is able to provide a reasonably quiet reference potential so that signals from single electrodes can be measured in relative isolation. It would also be desirable to minimize the number of electrodes required for the system. This could be accomplished by utilizing all of the electrodes for sensing the signal of interest. Furthermore, it would be desirable to avoid the need for placing a reference electrode at a distant location from other electrodes positioned near the source of the signal of interest.
It would be further desirable to minimize artifact caused by myographic potentials, or by environmental static potentials. It would also be desirable to minimize electrical potentials generated in the body of a patient due to operation of the component circuitry, as well as any residual current leaking from the device into the patient. Furthermore, it would be desirable to provide techniques for automatically detecting mechanical and/or electrical failure of the sensing device, so that appropriate actions may be taken to address such failure.
In accordance with embodiments of the present invention, an apparatus for amplifying a plurality N of inputs to generate N outputs is provided. The apparatus comprises: a first stage amplifier for amplifying each of the N inputs relative to a first common reference to generate N intermediate outputs, the first common reference comprising the average of the N inputs; and a second stage amplifier for amplifying each of the N intermediate outputs relative to a second common reference to generate the N outputs, the second stage amplifier comprising the average of the N intermediate outputs.
In accordance with embodiments of the present invention, an apparatus for amplifying a plurality N of inputs to generate N outputs is provided, the apparatus comprising: an amplifier for amplifying each of the N inputs relative to a common reference to generate the N outputs, the common reference comprising the average of the N inputs; and a memory coupled to the N outputs, the memory configured to record each of the N outputs.
In accordance with embodiments of the present invention, an apparatus is provided, comprising: a plurality N of electrical input leads; and an amplifier for amplifying voltages at each of the N electrical input leads relative to a common reference to generate N outputs, the common reference comprising the average of the N inputs; wherein each of the N electrical input leads is coupled to a corresponding physiological signal source to be measured.
In accordance with embodiments of the present invention, an apparatus is provided, comprising: a plurality N of electrical input leads; and an amplifier for amplifying voltages at each of the N electrical input leads relative to a common reference to generate N outputs, the common reference comprising the average of the N inputs; wherein none of the N electrical input leads is coupled to a designated reference electrode.
In accordance with embodiments of the present invention, a method is provided comprising: coupling a plurality N of inputs to a physiological signal source; and amplifying the N inputs relative to a common reference to generate N outputs, the common reference comprising the average of the N inputs.
In accordance with embodiments of the present invention, an apparatus for amplifying a plurality N of inputs to generate N outputs is provided, the apparatus comprising: an amplifier for amplifying each of the N inputs relative to a common reference to generate the N outputs, the common reference comprising the average of the N inputs; and a signal processing module configured to process the plurality of output voltages, the signal processing module comprising: a summation module configured to sum the plurality of output voltages; an out-of-range detection module configured to detect when the output of the summation module exceeds a pre-defined range.
In accordance with embodiments of the present invention, a method is provided, comprising: amplifying a plurality N of input voltages using a first stage to generate N first voltages, the amplifying comprising referencing each of the N input voltages to a first common voltage reference, the first common voltage reference comprising the average of the plurality N of input voltages; and amplifying the N first voltages using a second stage to generate N output voltages, the amplifying the N first voltages comprising referencing each of the N first voltages to a second common voltage reference, the second common voltage reference comprising the average of the N first voltages.
In accordance with embodiments of the present invention, an apparatus is provided, comprising: a plurality N of input conducting leads; and amplifier means to amplify the voltages at each of the plurality N of input conducting leads referenced to a common voltage, the common voltage comprising the average of the voltages at the plurality N of input conducting leads.
In accordance with embodiments of the present invention, an apparatus is provided, comprising: a housing; a plurality of input conducting leads; and a plurality of amplifier modules contained in the housing, each amplifier module comprising an input node coupled to a corresponding one of the plurality of input conducting leads, each amplifier module further comprising at least one corresponding output node; wherein a bias node conductively couples a bias voltage to the input node of each amplifier module.
The detailed description set forth below in connection with the appended drawings is intended as a description of exemplary embodiments of the present invention and is not intended to represent the only exemplary embodiments in which the present invention can be practiced. The term “exemplary” used throughout this description means “serving as an example, instance, or illustration,” and should not necessarily be construed as preferred or advantageous over other exemplary embodiments. The detailed description includes specific details for the purpose of providing a thorough understanding of the exemplary embodiments of the invention. It will be apparent to those skilled in the art that the exemplary embodiments of the invention may be practiced without these specific details. In some instances, well known structures and devices are shown in block diagram form in order to avoid obscuring the novelty of the exemplary embodiments presented herein.
In this specification and in the claims, it will be understood that when an element is referred to as being “connected to” or “coupled to” another element, it can be directly connected or coupled to the other element or intervening elements may be present. In contrast, when an element is referred to as being “directly connected to” or “directly coupled to” another element, there are no intervening elements present. When two elements are referred to as being “conductively coupled” to one another, then the two elements are coupled by a path having non-zero conductance, or finite resistance. For example, there may be a short-circuit path (i.e., a path of very high conductance) between two “conductively coupled” elements, or there may be a resistive path between such two “conductively coupled” elements.
In
The input to each amplifier module 151.n may be biased by a reference voltage Vref through a corresponding resistor R1.n, also denoted a bias resistance. The amplifier modules 151.1 through 151.N collectively amplify input voltages at IN.1 through IN.N to generate output voltages at OUT.1 through OUT.N, which are provided to a signal processing module 160. The module 160 may perform further signal conditioning on the amplifier module outputs, as well as analog-to-digital conversion for further processing by a digital computational module (not shown).
Note the amplifier modules 151.1 through 151.N shown in
The apparatus 100 may amplify and process the plurality of input voltages IN.1 through IN.N without necessarily referencing a common voltage, e.g., a ground voltage.
In
In an exemplary embodiment, the bias voltage Vref may be chosen to be at approximately halfway between supply voltages used to power the amplifiers 220 and 230, thereby maximizing the available signal swing at the non-inverting input nodes to both op amps.
In
In
It will be appreciated that the topology shown in
By eliminating the need to provide a physically separate reference voltage, as earlier described in the Background section, the amplifier architecture of
Note the configuration of amplifiers 220.1 through 220.N, along with feedback networks, may be referred to as a composite “first-stage amplifier” in the present disclosure, and in the claims. Similarly, amplifiers 230.1 through 230.N, along with feedback networks, may be referred to as a composite “second-stage amplifier.”
In an aspect of the present disclosure, input protection circuitry is further provided to the apparatus 100 to protect against possible adverse electrical events.
It will be appreciated that the diodes 370.1 through 370.N may function to prevent excessive voltage from being built up between any of inputs IN.1 through IN.N. Note the connection of node 400a to Vref through resistor R3 keeps corresponding input nodes IN.1 through IN.N biased within the range of the input protection devices 410, and eliminates the voltage across diodes 370.1 through 370.N and hence leakage through them, thereby also reducing unwanted noise generation. One of ordinary skill in the art will appreciate that in alternative exemplary embodiments, other devices may be used in place of the bidirectional Zener diodes shown, e.g., unidirectional Zener diodes, other clamping devices known in the art, etc.
Further shown in
Note in alternative exemplary embodiments, other resistive networks (not shown) may be provided in place of, or in addition to, R3 and R4 shown in
In an exemplary embodiment, for further protection from large voltages accumulating between the housing 110 and any other circuit element, an air gap may be provided between the housing 110 and any reference voltage or any circuit element protected against static discharge, e.g. any of the Zener diodes shown in
The air gap 490 may be implemented by limiting the physical separation between the housing 110 and the node 400a to be less than a maximum distance, e.g., 1 millimeter. The air gap 490 thus effectively acts as a parallel path to the resistance R4 to discharge any large voltage potentials between the housing 110 and the node 400a through electrical arcing resulting from breakdown of a gas medium, e.g., helium, between the housing 110 and the node 400a.
In a further aspect of the present disclosure, input impedance measurement capability is provided for the apparatus 100.
In an exemplary embodiment, measurement of the impedance between any two input nodes IN.x and IN.y, wherein x and y are each an integer index from 1 to N, and x y, may proceed as described hereinbelow. In an illustrative case wherein x=1 and y=2, a first voltage VCAL.1 may be coupled to the node 510.1 via resistor R7.1, while a second voltage VCAL.2≠VCAL.1 may be coupled to the node 510.2 via resistor R7.2. By measuring the voltage difference between nodes IN.1 and IN.2 using amplifiers 151.1 and 151.2, an indication of the impedance between the nodes 510.1 and 510.2 may be derived.
It will be appreciated that by appropriately setting the calibration voltages VCAL.x and VCAL.y, measure the impedance between any two input nodes IN.x and IN.y may be measured. In an exemplary embodiment, the calibration voltage generation module 520 may be, e.g., a microprocessor having N separate DAC outputs that can generate programmable voltage levels. In an exemplary embodiment, the calibration voltage generation module 520 may further be provided with current measurement capability to measure the current flowing through each voltage source VCAL.1 through VCAL.N.
In
In
At block 720, the first voltage VCAL.x is coupled to the calibration node CAL of a first amplifier module 151.x.
At block 730, a second voltage VCAL.y=VLO is further generated by the calibration voltage generation module 520.
At block 740, the second voltage VCAL.y is coupled to the calibration node CAL of a second amplifier module 151.y.
At block 750, the output voltages OUT.x and OUT.y of amplifier modules 151.x and 151.y are measured to determine a voltage drop across IN.x and IN.y, which also provides an indication of the impedance between IN.x and IN.y.
In an exemplary embodiment, by calculating the impedance present between the IN nodes of two amplifier modules in the apparatus 100.2, i.e., the electrode contact impedance, mechanical or electrical failures resulting in, e.g., a short circuit between the inputs of two amplifier modules may be detected. Furthermore, when the apparatus 100.2 including terminals 120.1 through 120.N is implanted in a patient body, and placed in contact with, e.g., body tissue or fluid, the measured electrode contact impedance between two terminals may represent the signal source impedance of the body tissue or fluid. Data on the signal source impedance may be utilized by, e.g., the signal processing module 160, to more accurately process the voltage outputs of the amplifier modules, according to techniques derivable by one of ordinary skill in the art.
In a further aspect of the present disclosure, techniques are provided to identify mechanical and/or electrical anomalies when multiple amplifier modules are configured to amplify the difference between their corresponding inputs and the average of all amplifier module inputs. In an exemplary embodiment, each amplifier module output OUT.n is configured to be proportional (over the pass-band of the amplifier module) to the difference between the corresponding amplifier module input IN.n and the average of all amplifier module inputs IN.1 through IN.N. In this case, it is expected that the instantaneous sum of all amplifier module outputs OUT.1 through OUT.N may be equal to zero or to a reference voltage VA during normal operation. By computing the sum of the amplifier module outputs, and determining whether the sum deviates significantly from zero, anomalies in the amplifier module operation, e.g., mechanical and/or electrical anomalies, may be identified.
In an exemplary embodiment, the plurality of conductive leads 120.1 through 120.N, along with corresponding insulating sheaths 122.1 through 122.N, not shown in
In exemplary embodiments, the conducting leads may be simultaneously or alternatively configured as described in co-pending U.S. Patent Publication No. 2008/0183097 A1, application Ser. No. 12/020,507, entitled “Methods and Systems for Measuring a Subject's Susceptibility to a Seizure,” filed Jan. 25, 2008, pending; U.S. patent application Ser. No. 12/630,300, entitled “Universal Electrode Array for Monitoring Brain Activity,” filed Dec. 3, 2009; and U.S. patent application Ser. No. 12/685,543, filed Jan. 11, 2010, entitled “Medical Lead Termination Sleeve for Implantable Medical Devices,” all of which are assigned to the assignee of the present disclosure, the contents of which are hereby incorporated in their entireties.
In
In one aspect, the neural signals of the patient are sampled substantially continuously with the electrodes coupled to the electronic components of the implanted leadless device. In particular, electrical signal amplification and sampling may be performed by an apparatus such as that described hereinabove with reference to, e.g.,
A wireless signal is transmitted that is encoded with data that is indicative of the sampled neural signal from the implanted device to an external device. The wireless signal can be any type of wireless signal, e.g., radiofrequency signal, magnetic signal, optical signal, acoustic signal, infrared signal, etc.
The physician may implant any desired number of devices in the patient. As noted above, in addition to monitoring brain signals, one or more additional implanted devices 62 may be implanted to measure other physiological signals from the patient.
The implantable device 62 may be configured to substantially continuously sample the brain activity of the groups of neurons in the immediate vicinity of the implanted device 62. The implantable device 62 may be interrogated and powered by a signal from an external device 64 to facilitate the substantially continuous sampling of the brain activity signals. Each sample of the patient's brain activity may contain between about 8 bits per sample and about 32 bits per sample, and preferably between about 12 bits per sample and about 16 bits per sample.
In alternative embodiments, it may be desirable to have the implantable devices sample the brain activity of the patient on a non-continuous basis. In such embodiments, an implantable device 62 may be configured to sample the brain activity signals periodically (e.g., once every 10 seconds) or aperiodically.
The implantable device 62 may include a separate memory module for storing the recorded brain activity signals, a unique identification code for the device, algorithms, other programming, or the like.
A patient instrumented with the implanted device 62 may carry a data collection device 64 that is external to the patient's body. The external device 64 would receive and store the signals from the implanted device 62 with the encoded EEG data (or other physiological signals). The signals received from the implanted device 62 may be represented as a multi-channel signal. The external device 64 is typically of a size so as to be portable and carried by the patient in a pocket or bag that is maintained in close proximity to the patient. In alternative embodiments, the device may be configured to be used in a hospital setting and placed alongside a patient's bed. Communication between the data collection device 64 and the implantable device 62 may take place through wireless communication. The wireless communication link between implantable device 62 and external device 64 may provide a communication link for transmitting data and/or power. External device 64 may include a control module 66 that communicates with the implanted device through an antenna 68. In the illustrated embodiment, antenna 68 is in the form of a necklace that is in communication range with the implantable devices 62.
Transmission of data and power between implantable device 62 and external device 64 may be carried out through a radiofrequency link, infrared link, magnetic induction, electromagnetic link, Bluetooth® link, Zigbee link, sonic link, optical link, other types of wireless links, or combinations thereof.
In an exemplary embodiment, the external device 64 may include software to pre-process the data according to the present disclosure and analyze the data in substantially real-time. For example, the received RF signal with the sampled EEG may be analyzed for the presence of anomalies according to the present disclosure, and further by EEG analysis algorithms to estimate the patient's brain state which is typically indicative of the patient's propensity for a neurological event. The neurological event may be a seizure, migraine headache, episode of depression, tremor, or the like. The estimation of the patient's brain state may cause generation of an output. The output may be in the form of a control signal to activate a therapeutic device (e.g., implanted in the patient, such as a vagus nerve stimulator, deep brain or cortical stimulator, implanted drug pump, etc.).
In an exemplary embodiment, the output may be used to activate a user interface on the external device to produce an output communication to the patient. For example, the external device may be used to provide a substantially continuous output or periodic output communication to the patient that indicates their brain state and/or propensity for the neurological event. Such a communication could allow the patient to manually initiate self-therapy (e.g., wave wand over implanted vagus nerve stimulator, cortical, or deep brain stimulator, take a fast acting anti-epileptic drug, etc.).
In an alternative exemplary embodiment, the external device 64 may further communicate with an auxiliary server (not shown) having more extensive computational and storage resources than can be supported in the form factor of the external device 64. In such an exemplary embodiment, anomaly pre-processing and EEG analysis algorithms may be performed by an auxiliary server, or the computations of the external device 64 may be otherwise facilitated by the computational resources of the auxiliary server.
In the embodiment shown in
As shown in
The electrode arrays 112 may comprise one or more contacts for collecting the neurological signals. The electrode arrays 112 of the present invention may be intracranial electrodes (e.g., epidural, subdural, and/or depth electrodes), extracranial electrodes (e.g., spike or bone screw electrodes, subcutaneous electrodes, scalp electrodes, dense array electrodes), or a combination thereof. While it is preferred to monitor signals directly from the brain, it may also be desirable to monitor brain activity using sphlenoidal electrodes, foramen ovale electrodes, intravascular electrodes, peripheral nerve electrodes, cranial nerve electrodes, or the like. While the disclosure herein may focus on intracranial electrodes for sampling intracranial EEG, it should be appreciated that the present invention encompasses any type of electrodes that may be used to sample any type of physiological signal from the subject. It will be appreciated that the electrical potentials as sampled by the electrode arrays 112 may be coupled to input conductive leads and processed according to the techniques described in the present disclosure. In an aspect, the neural signals of the patient are sampled substantially continuously with the electrodes coupled to the electronic components of the implanted leadless device. In particular, electrical signal amplification and sampling may be performed by an apparatus such as that described hereinabove with reference to, e.g.,
In the configuration illustrated in
In an exemplary embodiment, the implanted assembly 114 may include software to pre-process the data according to the present disclosure and analyze the data in substantially real-time. For example, the sampled EEG from the electrode arrays 112 may be analyzed for the presence of anomalies according to the present disclosure, and further by EEG analysis algorithms to estimate the patient's brain state which is typically indicative of the patient's propensity for a neurological event. The neurological event may be a seizure, migraine headache, episode of depression, tremor, or the like. The estimation of the patient's brain state may cause generation of an output. The output may be in the form of a control signal to activate a therapeutic device (e.g., implanted in the patient, such as a vagus nerve stimulator, deep brain or cortical stimulator, implanted drug pump, etc.).
In an exemplary embodiment, the implanted assembly 114 may further wirelessly communicate with an external device 120 to activate a user interface and produce an output communication to the patient. For example, the external device 120 may be used to provide a substantially continuous output or periodic output communication to the patient that indicates their brain state and/or propensity for the neurological event. Such a communication could allow the patient to manually initiate self-therapy (e.g., wave wand over implanted vagus nerve stimulator, cortical, or deep brain stimulator, take a fast acting anti-epileptic drug, etc.).
In an alternative exemplary embodiment, the external device may further communicate with an auxiliary server (e.g., server 126) having more extensive computational and storage resources than can be supported in the form factor of the external device. In such an exemplary embodiment, anomaly pre-processing and EEG analysis algorithms may be performed by an auxiliary server 126, or the computations of the external device may be otherwise facilitated by the computational resources of the auxiliary server 126.
Described above are techniques for amplifying a plurality of input voltages to generate a corresponding plurality of output voltages, in which each of the plurality of input voltages is referenced to a common voltage comprising the average of the plurality of input voltages, without the need to reference an externally provided common voltage. These techniques may be particularly useful when averaging a large number of input voltages, such as in the sixteen channel embodiments described above. If the signals on each channel are independent, the amplitude of N averaged signals is expected to be 1/(sqrt(N)) than that from a single channel. Therefore, when using sixteen independent channels, the averaged signal is expected to be 1/(sqrt(16))=¼ than that of a single channel. However, it may be desirable to use a modified version of these techniques in certain situations.
Some exemplary configurations of the electrode arrays 112 are shown in
Each lead 1212 has a proximal end coupled to an implanted collection device 1216. The implanted collection device 1216 comprises a hermetically sealed housing containing electronics for detecting and storing the physiological signals being monitored. In an exemplary embodiment, the housing may be made of titanium, ceramic, or other biocompatible material. In the illustrated embodiment, the leads 1212 are fixedly coupled to the collection device 1216. In other embodiments, the collection device 1216 includes a connector permitting the surgeon to attach or detach the leads 1212 from the collection device 1216.
The leads 1212 may take any of a variety of forms suitable for detecting the physiological signal to be monitored. Each lead 1212 is configured to come in direct physical contact with biological tissue or fluid inside the body of a patient, to sense electrical potentials present on such tissue or fluid. In the illustrated embodiment, the leads 1212 are cylindrical micro-leads approximately 1.5 mm in diameter with cylindrical contacts 14. In other embodiments, the leads 1212 may be provided in other shapes and designs, such as a strip electrode array, grid electrode array, or depth electrodes. The size and shape of each contact 1214 may also vary in different embodiments, depending on the type of signal being monitored.
In the embodiment illustrated in
The eight reference contacts 312a-312h are coupled to a single proximal reference contact 322 via a single reference lead (not shown) which carries the signals through the lead body 304.
EEG signals are typically contaminated by various artifacts unrelated to the neurological signals of interest, for example, in a monitoring device for epilepsy patients. Electromyographic (EMG) artifacts are particularly prominent when the electrical signals are detected extracranially, such as when using externally-placed scalp electrodes, or implanted electrodes positioned outside of the skull. When designing a neurological monitoring system, it would be desirable to configure the system and its electrodes to optimize EEG detection while suppressing EMG contamination.
As a general matter, when two electrodes are positioned close together, the physiological signals detected by each electrode look similar. As the two electrodes are positioned farther apart, the differences in the physiological signals detected by each electrode increase.
When positioning electrodes extracranially, the electrode contacts are relatively far away from the EEG generators (i.e., the neurons of the brain), but close to the EMG generators (i.e., muscles in the head). Accordingly, as the distance between two extracranial electrodes increases, the EMG should decorrelate with distance faster than the EEG.
In a lead assembly comprising a linear array of N electrodes, with a spacing of X between adjacent electrodes, it may be desirable to select X and N such that the electrode array is relatively “close together” for EEG but at the same time adjacent electrode contacts are relatively “far apart” for EMG. X may be selected to be at least the minimum distance necessary to decorrelate at least a portion of the EMG signal between adjacent contacts, and N may be selected to be the number of contacts such that the EEG signal on the first contact is still reasonably well correlated with the EEG signal on the Nth contact.
The eight reference contacts 312a-312h may be summed together by connecting them to a single proximal reference contact 322. The signal from this single proximal reference contact 322 may be used alone or in combination of one or more of the other channels of data from the signal contacts 314a-314d to generate the common reference voltage for the amplification of the input signals.
The signal from the reference contact 322 may be detected in a variety of ways. For example, eight separate reference contacts 312a-312h may be connected to the same lead wire. Alternatively, a single large contact 312 may be masked so as to detect signals from multiple disparate locations. Alternatively, a single, elongate contact may be provided along the length of the contact region 302.
In embodiments described above with respect to
In accordance with some embodiments, the positioning and orientation of an array of electrodes may be selected so as to further improving EEG detection while minimizing EMG artifact.
For many epilepsy patients, it is desirable to monitor EEG signals from the temporal lobe. Therefore, for a monitoring system using extracranial electrodes, the electrodes may be positioned adjacent to the temporalis muscle.
Based on the teachings described herein, it should be apparent that an aspect disclosed herein may be implemented independently of any other aspects and that two or more of these aspects may be combined in various ways. In one or more exemplary embodiments, the functions described may be implemented in hardware, software, firmware, or any combination thereof. If implemented in software, the functions may be stored on or transmitted over as one or more instructions or code on a computer-readable medium. Computer-readable media includes both computer storage media and communication media including any medium that facilitates transfer of a computer program from one place to another. A storage media may be any available media that can be accessed by a computer. By way of example, and not limitation, such computer-readable media can comprise RAM, ROM, EEPROM, CD/DVD-ROM or other optical disk storage, magnetic disk storage or other magnetic storage devices, solid-state flash cards or drives, or any other medium that can be used to carry or store desired program code in the form of instructions or data structures and that can be accessed by a computer. Also, any connection is properly termed a computer-readable medium. For example, if the software is transmitted from a website, server, or other remote source using a coaxial cable, fiber optic cable, twisted pair, digital subscriber line (DSL), or wireless technologies such as infrared, radio, and microwave, then the coaxial cable, fiber optic cable, twisted pair, DSL, or wireless technologies such as infrared, radio, and microwave are included in the definition of medium. Disk and disc, as used herein, includes compact disc (CD), laser disc, optical disc, digital versatile disc (DVD), floppy disk and Blu-Ray disc where disks usually reproduce data magnetically, while discs reproduce data optically with lasers. Combinations of the above should also be included within the scope of computer-readable media.
A number of aspects and examples have been described. However, various modifications to these examples are possible, and the principles presented herein may be applied to other aspects as well.
The present application is a continuation-in-part of U.S. patent application Ser. No. 13/441,609, filed Apr. 6, 2012, which claims the benefit of U.S. Provisional Application No. 61/473,639, filed Apr. 8, 2011; and further claims the benefit of U.S. Provisional Patent Application No. 61/756,330, filed Jan. 24, 2013, and U.S. Provisional Patent Application No. 61/756,319, filed Jan. 24, 2013, the complete disclosures of which are incorporated by reference herein in their entirety.
Number | Date | Country | |
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61473639 | Apr 2011 | US | |
61756319 | Jan 2013 | US | |
61756330 | Jan 2013 | US |
Number | Date | Country | |
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Parent | 13441609 | Apr 2012 | US |
Child | 14163117 | US |