Patent Grant
8543199
The present invention relates generally to systems and methods for monitoring a subject's neurological condition. More specifically, the present invention is related to minimally invasive methods and systems for monitoring a subject who has epilepsy and determining if the subject is in a contra-ictal condition in which the subject is at low susceptibility for a seizure and is unlikely to transition into a pre-seizure condition within a computed or predetermined time period.
Epilepsy is a disorder of the brain characterized by chronic, recurring seizures. Seizures are a result of uncontrolled discharges of electrical activity in the brain. A seizure typically manifests itself as sudden, involuntary, disruptive, and often destructive sensory, motor, and cognitive phenomena. Seizures are frequently associated with physical harm to the body (e.g., tongue biting, limb breakage, and burns), a complete loss of consciousness, and incontinence. A typical seizure, for example, might begin as spontaneous shaking of an arm or leg and progress over seconds or minutes to rhythmic movement of the entire body, loss of consciousness, and voiding of urine or stool.
A single seizure most often does not cause significant morbidity or mortality, but severe or recurring seizures (epilepsy) results in major medical, social, and economic consequences. Epilepsy is most often diagnosed in children and young adults, making the long-term medical and societal burden severe for this population of subjects. People with uncontrolled epilepsy are often significantly limited in their ability to work in many industries. An uncommon, but potentially lethal form of seizure is called status epilepticus, in which a seizure continues for more than 30 minutes. This continuous seizure activity may lead to permanent brain damage, and can be lethal if untreated.
While the exact cause of epilepsy is often uncertain, epilepsy can result from head trauma (such as from a car accident or a fall), infection (such as meningitis), or from neoplastic, vascular, or developmental abnormalities of the brain. Most epilepsy, especially most forms that are resistant to treatment (i.e., refractory), are idiopathic or of unknown causes, and are generally presumed to be an inherited genetic disorder. Demographic studies have estimated the prevalence of epilepsy at approximately 1% of the population, or roughly 2.5 million individuals in the United States alone. Approximately 60% of these subjects have focal epilepsy where a defined point of onset can be identified in the brain and are therefore candidates for some form of a focal treatment approach.
If it is assumed that an “average” subject with focal epilepsy has between 3 and 4 seizures per month, in which each of the seizures last for several seconds or minutes, the cumulative time the subject would be seizing is only about one hour per year. The other 99.98% of the year, the epileptic subject is free from seizures. The debilitating aspect of epilepsy is the constant uncertainty of when the next seizure is going to strike. It is this constant state of uncertainty which causes epileptic subjects to remove themselves from society. It is the constant fear and uncertainty of when the next seizure will strike that prevents the person from performing activities that most non-epileptic subjects take for granted.
To that end, there have been a number of proposals from groups around the world for predicting seizures and warning the subject of the impending seizure. Most of such proposals attempt to analyze the subject's electroencephalogram or electrocorticograms (referred to collectively as “EEGs”), to differentiate between a “pre-ictal condition” (i.e., pre-seizure condition) and an “inter-ictal condition” (i.e., between seizures). To date, however, none of the proposed systems have proven to be effective in predicting seizures. Some researchers have proposed that seizures develop minutes to hours before the clinical onset of the seizure. These researchers therefore classify the pre-ictal condition as the beginning of the ictal or seizure event which begins with a cascade of events. Under this definition, a seizure is imminent and will occur if a pre-ictal condition is observed. Others believe that a pre-ictal condition represents a state which only has a high susceptibility for a seizure and does not always lead to a seizure, and that seizures occur either due to chance (e.g., noise) or via a triggering event during this high susceptibility time period. For clarity, the term “pro-ictal” is introduced here to represent a state or condition that represents a high susceptibility for seizure; in other words, a seizure can happen at any time. Ictal activity, within the scope of epilepsy, refers to seizure activity. Ictal activity may have other meanings in other contexts.
Prior art seizure detection and warning systems focused only on the identification of ictal or pro-ictal physiological data from the subject. See, e.g., Litt U.S. Pat. No. 6,658,287. While being able to determine that the subject is in a “pro-ictal” condition is highly desirable, identifying when the subject has entered or is likely to enter a pro-ictal condition is only part of the solution for these subjects. An equally important aspect of any seizure advisory system is the ability to be able to inform the subject when they are unlikely to have a seizure for a predetermined period of time (e.g., low susceptibility or “contra-ictal”). Simply knowing that the subject is not pro-ictal does not provide the subject with the assurance that they will not quickly transition into a pro-ictal or ictal condition. Knowing that they are in a contra-ictal state can allow the subject to engage in normal daily activities, such as walking down a set of stairs, without fearing that they will have a seizure. Knowing when a seizure is unlikely to occur can be even more important for the subject's sense of freedom than being alerted when a seizure is likely to occur.
Furthermore, for one reason or another, it may not be possible to accurately predict the seizures in a portion of the subject population. However, for that same portion of the subject population, it may be possible to let the subject know when they are unlikely to have a seizure for a period of time.
Accordingly, it would be desirable to provide methods and systems that are able to inform the subject that they are highly unlikely to transition into a pro-ictal or ictal condition in a period of time. It would further be desirable if such systems and methods could substantially continuously provide an output to the subject in a minimally invasive fashion to differentiate when the subject is at a low susceptibility to seizure, raised susceptibility to seizure, and/or a high susceptibility to seizure.
Systems and methods are described herein for identifying a state or condition in which the subject is unlikely to transition to an ictal state or condition within a time period. Such a state is described herein as a “contra-ictal” condition or state. If it is determined that the subject is in the contra-ictal state, a communication is output to the subject that is indicative of the subject being in the contra-ictal state.
In some embodiments, the present invention may provide a substantially continuous output to the subject that indicates the subject's real-time susceptibility to a seizure for a time period. The output may provide an indication that the subject is at a high susceptibility to a seizure (e.g., seizure prediction or determination of being in a pre-ictal condition), a mild or normal susceptibility to a seizure (e.g., the subject is in an inter-ictal state), or a low susceptibility to a seizure (e.g., the subject appears to be highly unlikely to have a seizure within a time period).
The term “state” is used herein to generally refer to calculation results or indices that are reflective of the state of the subject's neural system, but does not necessarily constitute a complete or comprehensive accounting of the subject's total neurological condition. The estimation and characterization of “state” may be based on one or more subject dependent parameters from the brain, such as electrical signals from the brain, including but not limited to electroencephalogram signals “EEG” and electrocorticogram signals “ECoG” (referred to herein collectively as “EEG”), brain temperature, blood flow in the brain, concentration of anti-epileptic drugs (AEDs) in the brain, or other physiological signals.
The term “pro-ictal” is used herein to refer to a neurological state or condition characterized by an increased likelihood of transition to an ictal state. A pro-ictal state may transition to either an ictal or inter-ictal state. A pro-ictal state that transitions to an ictal state is also referred to as pre-ictal.
Minimally-invasive systems that provide for the long-term, ambulatory monitoring of subject's brain activity are described. These systems will typically include one or more implantable devices that may be minimally invasively implanted in the subject. The implantable device may be adapted to sample a physiological signal from a subject. A processing assembly processes a data signal from the implantable device to determine if the subject is in a contra-ictal condition. If the subject is determined to be in a contra-ictal condition, a user interface provides an output to the subject that indicates that the subject is in the contra-ictal condition.
The data signal can be indicative of the physiological signal and can be substantially continuously transmitted substantially in real-time from the implanted minimally invasive leadless device to the processing assembly. The data signal can comprise a compressed EEG signal or an encrypted EEG signal, or it may comprise an extracted feature from a physiological signal from the subject. The user interface can provide a substantially continuous output to the subject regarding the subject's condition.
The minimally invasive leadless device can be in wireless communication with the processing assembly. The processing assembly and the user interface can both be part of a patient handheld device.
The contra-ictal condition can include a condition in which the subject is at a low susceptibility to having a seizure within a time period.
The output to the subject that indicates that the subject is in the contra-ictal condition can comprise an audible output, a tactile output, a visual output on a display, or a combination thereof. The output to the subject can comprise, e.g., a green light.
In another embodiment, a seizure advisory system is provided comprising an implanted leadless device that is configured to sample an EEG signal (or other physiological signal) from a subject and transmit a wireless signal from the subject's body to a subject advisory device that is external to the subject's body. The subject advisory device comprises a processing assembly that processes the wireless signal to determine if the subject is in a contra-ictal condition. If the user is determined to be in a contra-ictal condition, a user interface of the subject advisory device provides an output to the subject that indicates that the subject is in the contra-ictal condition.
The subject advisory device can comprise a memory for storing the wireless signal. The contra-ictal condition can be a neurological state in which the subject is unlikely to transition into an ictal condition within a time period. The time period can be a predetermined time period.
The leadless device can be adapted to be implanted between the subject's dura and scalp, and preferably between the subject's skull and scalp.
In yet another embodiment, a method of monitoring a subject's neurological condition is provided. The method comprises implanting a device in the subject. In one embodiment, the device is implanted in a minimally invasive fashion. Typically, the devices are leadless and are implanted between a subject's skull and scalp. A physiological signal sampled by the implanted devices is analyzed to determine if the subject is in a contra-ictal condition. If the subject is in a contra-ictal condition, an output is provided to the subject that is indicative of the subject being in the contra-ictal condition.
The physiological signal can be an EEG signal. The contra-ictal condition can be a neurological state in which the subject is unlikely to transition into an ictal condition within a time period. The time period can be a predetermined time period.
Analyzing the physiological signal can comprise extracting N features from the physiological signal, generating a N-dimensional feature vector of the extracted N features for time points of the physiological signal, and determining if the N-dimensional feature vector is within a contra-ictal cluster or region in the N-dimensional space.
For a further understanding of the nature and advantages of the present invention, reference should be made to the following description taken in conjunction with the accompanying drawings.
All publications, patents, and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication, patent, or patent application was specifically and individually indicated to be incorporated by reference.
Certain specific details are set forth in the following description and figures to provide an understanding of various embodiments of the invention. Certain well-known details, associated electronics and devices are not set forth in the following disclosure to avoid unnecessarily obscuring the various embodiments of the invention. Further, those of ordinary skill in the relevant art will understand that they can practice other embodiments of the invention without one or more of the details described below. Finally, while various processes are described with reference to steps and sequences in the following disclosure, the description is for providing a clear implementation of particular embodiments of the invention, and the steps and sequences of steps should not be taken as required to practice this invention.
While the discussion below focuses on measuring electrical signals generated by electrodes placed near, on, or within the brain or nervous system (EEG signals) of subjects and subject populations for the determination of when an epileptic subject is in a contra-ictal condition, it should be appreciated that the invention is not limited to measuring EEG signals or to determining when the subject is in a contra-ictal state. For example, the invention could also be used in systems that measure one or more of a blood pressure, blood oxygenation (e.g., via pulse oximetry), temperature of the brain or of portions of the subject, blood flow measurements, ECG/EKG, heart rate signals, respiratory signals, chemical concentrations of neurotransmitters, chemical concentrations of medications, pH in the blood, or other physiological or biochemical parameters of a subject.
Furthermore, while the remaining discussion focuses on identifying a contra-ictal condition for epileptic subjects, the present invention may also be applicable to monitoring other neurological or psychiatric disorders and identifying a condition or state for such disorders in which the subject is unlikely to experience some adverse effect. For example, the present invention may also be applicable to monitoring and management of sleep apnea, Parkinson's disease, essential tremor, Alzheimer's disease, migraine headaches, depression, eating disorders, cardiac arrhythmias, bipolar spectrum disorders, or the like. As can be appreciated, the features extracted from the signals and used by the algorithms will be specific to the underlying disorder that is being managed. While certain features may be relevant to epilepsy, such features may or may not be relevant to the state measurement for other disorders.
One embodiment of the present invention identifies and uses a contra-ictal classification for each subject in which the subject is highly unlikely to transition to the ictal state within a specified time period. The contra-ictal condition can be considered to be a subset of the inter-ictal class or it can be considered to be a completely new neurological classification. While it is beneficial to the subject to know if the subject is in the inter-ictal condition, being in the inter-ictal condition does not necessarily inform the subject that they will not quickly transition from the inter-ictal condition to the ictal condition. Being able to inform a subject that they are in a contra-ictal state can allow the subject to engage in normal daily activities, such as walking down a set up stairs, without fearing that they will have a seizure or without fearing that they may quickly transition into a pro-ictal state. Knowing when a seizure is unlikely to occur can be even more important to the subject's freedom than being alerted when a seizure is likely to occur.
The period of time associated with the contra-ictal state will vary depending on the implementation of the algorithm. The period of time could be a predetermined time period as determined from the training data and programmed into the algorithm, such as 10 minutes, 20 minutes, 30 minutes, 60 minutes, 90 minutes or more. In other implementations, the algorithm could compute the period, which may be different from episode to episode for a single subject. Thus, for some subjects, the period of time could span many hours or even days or weeks.
Proposed seizure prediction systems only attempt to differentiate between a pre-ictal state and an inter-ictal state for purposes of seizure prediction. Advantageously, embodiments of the present invention may further identify the contra-ictal condition or state for the particular subject.
At step 2, a training dataset of the subject is obtained and annotated to identify the ictal activity. The training data could span days or weeks, and is preferably a substantially continuous monitoring of the subject's EEG signals using an array of scalp or intracranial electrodes. Preferably the training data comprises a plurality of ictal events separated by inter-ictal intervals. For epilepsy, the training set of physiological signals typically includes a training set of intracranial EEG recordings from the subject's long term visit to an epilepsy monitoring unit (EMU). However, the EEG training sets could be obtained from the ambulatory system utilizing an implantable device and external device as described below.
While EEG signals are currently the desirable physiological signals that are analyzed, any of the aforementioned physiological signals could be used to train the algorithms. As is known in the art, the training set may be overlaid with comments from a physician and/or a marking algorithm may automatically identify some or all of the ictal activity in the training set—such as epileptiform spikes, earliest electrographic change (EEC), unequivocal electrical onset of seizure (UEO), unequivocal clinical onset (UCO), end of electrographic seizure (EES), etc. The following Steps 4-10 which are described in the subsequent paragraphs are directed towards EEG signals, however, such analysis may also be applied to the aforementioned other physiological signals.
At step 4, N feature extractors may be applied to the training set to quantify relevant aspects of the EEG training dataset. Any number of features can be extracted from the EEG signals in order to assess the subject's condition. At step 6, for each desired point in time in the EEG training dataset, an N-dimensional feature vector will be formed for each of the N features that are extracted. At step 8, if desired, the extracted N-dimensional feature vectors may then be allocated or plotted in an N-dimensional feature space. While not shown in
Since it is not likely for the physician or training system to identify a contra-ictal period a priori, one aspect of the present invention utilizes an unsupervised learning protocol to identify a contra-ictal condition for the subject by utilizing an algorithm or other means to identify a region of the feature space or clusters or groupings of feature vectors in the N-dimensional feature space that are substantially devoid of feature vectors that are in an ictal condition and for which all feature vectors in the grouping or region are separated from an ictal event (e.g., seizure) by a predetermined time period (step 10). For example, the N-dimensional feature space may be partitioned into a collection of N-dimensional hypercubes. A hypercube that is substantially devoid of training vectors that occur within a predetermined time period prior to the next seizure may be labeled contra-ictal. In another implementation, a binary space partitioning algorithm can be used to partition the N-dimensional feature space into a collection of N-dimensional hyperprisms. A hyperprism that is substantially devoid of training vectors that occur within a predetermined time period prior to the next seizure may be labeled contra-ictal. In another implementation, the structure of the training data may be approximated by an expansion of radial basis function, e.g. a Gaussian mixture model. Each feature vector in the training data may be assigned to one component of the radial basis function expansion using, e.g., Bayesian posterior probability or decision risk criteria. A component that is substantially devoid of training vectors that occur within a predetermined time period prior to the next seizure may be labeled contra-ictal. The algorithm may also identify other classes of interest from the EEG training dataset (e.g., inter-ictal that is not part of the contra-ictal class, pro-ictal, ictal, post-ictal, or the like), and the classes of interest (or groupings of feature vectors) for the subject and/or mathematical representations thereof are stored in memory for later use in the subject system implanted or otherwise used by the subject.
It is further noted that each identified partition in the N-dimensional feature space can be assigned an identifier that may be used to represent states in a Markov chain, or symbols emitted by hidden states in a hidden Markov model. These identifiers, or sequences of identifiers may be used to make inferences about future states, and thereby the likelihood of seizure occurrence.
Similar approaches may be used to derive and train a pro-ictal algorithm. For example, an algorithm or other means may be used to identify a region of the feature space or clusters or groupings of feature vectors in the N-dimensional feature space that frequently precede an ictal state by a predetermined period of time but occur infrequently in inter-ictal intervals. Alternatively, a prior art seizure prediction algorithm may be used.
Once the algorithm has been trained to identify the different classes for the subject, the algorithm may be embodied or otherwise uploaded into a subject system for performing substantially real-time monitoring and assessment of the subject's brain activity.
The input data 12 is typically EEG, but may comprise representations of physiological signals obtained from monitoring a subject and may comprise any one or combination of the aforementioned physiological signals from the subject. The input data may be in the form of analog signal data or digital signal data that has been converted by way of an analog to digital converter (not shown). The signals may also be amplified, preprocessed, and/or conditioned to filter out spurious signals or noise. For purposes of simplicity the input data of all of the preceding forms is referred to herein as input data 12. In one preferred embodiment, the input data comprises between about 1 channel and about 64 channels of EEG from the subject.
The input data 12 from the selected physiological signals is supplied to the one or more feature extractors 14a, 14b, 15. Feature extractor 14a, 14b, 15 may be, for example, a set of computer executable instructions stored on a computer readable medium, or a corresponding instantiated object or process that executes on a computing device. Certain feature extractors may also be implemented as programmable logic or in a fixed logic device. In general, feature extractors 14a, 14b, 15 can process data 12 and identify some characteristic of interest in the data 12. Feature extractors used in the subject system are typically the same feature extractors used in the method described in the method of
Each feature extractor 14a, 14b, 15 may be univariate (operating on a single input data channel), bivariate (operating on two data channels), or multivariate (operating on multiple data channels). Some examples of potentially useful characteristics to extract from signals for use in determining the subject's propensity for a neurological event include but are not limited to bandwidth limited power (alpha band [8-13 Hz], beta band [13-18 Hz], delta band [0.1-4 Hz], theta band [4-8 Hz], low beta band [12-15 Hz], mid-beta band [15-18 Hz], high beta band [18-30 Hz], gamma band [30-48 Hz], high frequency power [>48 Hz], bands with octave or half-octave spacings, wavelets, etc.), second, third and fourth (and higher) statistical moments of the EEG amplitudes or other features, spectral edge frequency, decorrelation time, Hjorth mobility (HM), Hjorth complexity (HC), the largest Lyapunov exponent L(max), effective correlation dimension, local flow, entropy, loss of recurrence LR as a measure of non-stationarity, mean phase coherence, conditional probability, brain dynamics (synchronization or desynchronization of neural activity, STLmax, T-index, angular frequency, and entropy), line length calculations, first, second and higher derivatives of amplitude or other features, integrals, and mathematical linear and non-linear operations including but not limited to addition, subtraction, division, multiplication and logarithmic operations. Of course, for other neurological conditions, additional or alternative characteristic extractors may be used with the systems described herein.
The extracted characteristics can be supplied to the one or more classifiers 16, 17. Like the feature extractors 14a, 14b, 15, each classifier 16, 17 may be, for example, a set of computer executable instructions stored on a computer readable medium or a corresponding instantiated object or process that executes on a computing device. Certain classifiers may also be implemented as programmable logic or in a fixed logic device.
The classifiers 16, 17 analyze one or more of the extracted characteristics, and either alone or in combination with each other (and possibly other subject dependent parameters), provide a result 18 that may characterize, for example, a subject's condition. The output from the classifiers may then be used to determine the output communication that is provided to the subject regarding their condition. As described above, the classifiers 16, 17 are trained by exposing them to training measurement vectors, typically using supervised methods for known classes, e.g. ictal, and unsupervised methods as described above for classes that can't be identified a priori, e.g. contra-ictal. Some examples of classifiers include k-nearest neighbor (“KNN”), binary and higher order space partitions, linear or non-linear regression, Bayesian, mixture models based on Gaussians or other basis functions, neural networks, and support vector machines (“SVM”). Each classifier 16, 17 may provide a variety of output results, such as a logical result or a weighted result. The classifiers 16, 17 may be customized for the individual subject and may be adapted to use only a subset of the characteristics that are most useful for the specific subject. Additionally, over time, the classifiers 16, 17 may be further adapted to the subject, based, for example, in part on the result of previous analyses and may reselect extracted characteristics that are used for the specific subject.
For the embodiment of
Referring now to
The feature classification approach of
After deriving the feature vectors that may be used to classify subject physiological signals as being contra-ictal, pro-ictal, etc., these feature vectors may be used to train or form an algorithm for use in a patient monitoring device.
The truth table 50 of
It should be appreciated however, that while
Referring again to
At Time 2, the output 40 from the contra-ictal classifier is high (H) and the output from the pro-ictal classifier 42 is low (L). Such a classification indicates that there is a low likelihood that the subject has an increased susceptibility for a seizure and a high likelihood of being in a contra-ictal state. These classifiers appear to be consistent with each other; consequently, the output communication provided to the subject may indicate that the subject is in a contra-ictal state. One example of such an output communication is the display of a green light. This scenario corresponds to the second row 54 of
As shown in
Finally, at Time 4 in
In another embodiment shown in
While
In other embodiments, the output of the classification algorithm would indicate the existence of a contra-ictal condition (e.g., a green light) so long as the extracted feature vector corresponds only with training points that almost never preceded a seizure by less than the predetermined time period, such as 90 minutes. The output of the classification algorithm would indicate the existence of a pro-ictal condition (e.g., a red light) if the extracted feature corresponds to a region of the feature space indicative of pro-ictal state. This indication is not a seizure prediction; a pro-ictal condition might resolve without a seizure ever occurring. The end of a contra-ictal indication does indicate, however, that it is no longer unlikely that a seizure will occur within 90 minutes (or other predetermined time). In addition, in these embodiments, while the contra-ictal indication has a predetermined time associate with it, the pro-ictal indication does not. The subject may stay in a pro-ictal state for a prolonged period of time, or the subject might leave the pro-ictal state immediately after entering it.
In still other embodiments, the classification algorithm for a contra-ictal indication can be derived by determining the kinds of feature vectors that never preceded a pro-ictal condition by less than a predetermined time. When trained using this kind of subject data, this contra-ictal classification algorithm would indicate a contra-ictal condition (such as be lighting a green light) when a feature vector extracted from a subject's physiological signal (such as an EEG) corresponds to one of such feature vectors, thereby indicating that the subject is unlikely to transition to a pro-ictal state within that predetermined time period.
In yet other embodiments, the contra-ictal indication classification algorithm can be derived by determining the kinds of feature vectors that never preceded a pro-ictal condition by less than a predetermined time and never preceded a seizure by less than the predetermined time. When trained using this kind of subject data, this contra-ictal classification algorithm would indicate a contra-ictal condition (such as be lighting a green light) when a feature vector extracted from a subject's physiological signal (such as an EEG) corresponds to one of such feature vectors, thereby indicating that the subject is unlikely to transition to either a pro-ictal state or to a seizure within that predetermined time period.
The physician may implant any desired number of devices in the subject. In some embodiments between about 1 and about 32 channels are provided, and preferably between about 8 and about 16 channels are provided. 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 subject.
While it may be possible to implant the implantable devices 62 under the skull and in or on the brain, it is preferred to implant the implantable devices 62 in a minimally invasive fashion under at least one layer of the subject's scalp and above the skull. Implantable devices 62 may be implanted between any of the layers of the scalp (sometimes referred to herein as “sub-galeal”). For example, the implantable devices may be positioned between the skin and the connective tissue, between the connective tissue and the epicranial aponeurosis/galea aponeurotica, between the epicranial aponeurosis/galea aponeurotica and the loose areolar tissue, between the loose areolar tissue and the pericranium, and/or between the pericranium and the calvarium. In some configurations, it may be useful to implant different implantable devices 62 between different layers of the scalp.
Implantable devices 62 will typically be configured to substantially continuously sample the brain activity of the groups of neurons in the immediate vicinity of the implanted device. In some embodiments, if placed below the skull and in contact with the cortical surface of the brain, the electrodes may be sized to be able to sample activity of a single neuron in the immediate vicinity of the electrode (e.g., a microelectrode). Typically, the implantable device 62 will be interrogated and powered by a signal from the external device to facilitate the substantially continuous sampling of the brain activity signals. Sampling of the brain activity is typically carried out at a rate above about 200 Hz, and preferably between about 200 Hz and about 1000 Hz, and most preferably at about 400 Hz, but it could be higher or lower, depending on the specific condition being monitored, the subject, and other factors. Each sample of the subject's brain activity will typically 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. Thus, if each return communication transmission to the external device includes one EEG sample per transmission, and the sample rate is 400 Hz and there are 16 bits/sample, the data transfer rate from the implantable devices 62 to the external device 64 is at least about 6.4 Kbits/second. If there are 32 implantable devices, the total data transfer rate for the system 60 would be about 205 Kbits/second. In alternative embodiments, it may be desirable to have the implantable devices sample the brain activity of the subject in a non-continuous basis. In such embodiments, the implantable devices 62 may be configured to sample the brain activity signals periodically (e.g., once every 10 seconds) or aperiodically.
Implantable device 62 may comprise 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 subject instrumented with the implanted devices 62 will typically carry a data collection device 64 that is external to the subject's body. The external device 64 would receive and store the signal from the implanted device 62 with the encoded EEG data (or other physiological signals). The external device is typically of a size so as to be portable and carried by the subject in a pocket or bag that is maintained in close proximity to the subject. In alternative embodiments, the device may be configured to be used in a hospital setting and placed alongside a subject's bed. Communication between the data collection device 64 and the implantable device 62 typically takes 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. It should be appreciated however, that the configuration of antenna 68 and control module 66 may be in a variety of other conventional or proprietary forms. For example, in another embodiment control module 66 may be attached around an arm or belt of the subject, integrated into a hat, integrated into a chair or pillow, and/or the antenna may be integrated into control module 66.
In order to facilitate the transmission of power and data, the antenna of the external device and the implantable devices must be in communication range of each other. The frequency used for the wireless communication link has a direct bearing on the communication range. Typically, the communication range is between at least one foot, preferably between about one foot and about twenty feet, and more preferably between about six feet and sixteen feet. As can be appreciated, however, the present invention is not limited to such communication ranges, and larger or smaller communication ranges may be used. For example, if an inductive communication link is used, the communication range will be smaller than the aforementioned range.
In some situations, it may be desirable to have a wire directly connecting the subject-worn data collection device 64 to an interface (not shown) that could directly link up to the implanted devices 62 that are positioned below the subject's skin. For example, the interface may take the form of a magnetically attached transducer, as with cochlear implants. This could enable power to be continuously delivered to the implanted devices 62 and provide for higher rates of data transmission.
In some configurations, system 60 may include one or more intermediate transponders (not shown) that facilitates data transmission and power transmission between implantable device 62 and external device 64. The intermediate transponder may be implanted in the subject or it may be external to the subject. If implanted, the intermediate transponder will typically be implanted between the implantable device 62 and the expected position of the external device 64 (e.g., in the neck, chest, or head). If external, the transponder may be attached to the subject's skin, positioned on the subject's clothing or other body-worn assembly (e.g., eyeglasses, cellular phone, belt, hat, etc.) or in a device that is positioned adjacent the subject (e.g., a pillow, chair headrest, etc.). The intermediate transponder may be configured to only transmit power, only transmit data, or it may be configured to transmit both data and power. By having such intermediate transponders, the external device 64 may be placed outside of its normal communication range from the implanted devices 62 (e.g., on a subject's belt or in a subject's bag), and still be able to substantially continuously receive data from the implantable device 62 and/or transmit power to the implantable device 62.
Transmission of data and power between implantable device 62 and external device 64 is typically carried out through a radiofrequency link, but may also be carried out through magnetic induction, electromagnetic link, Bluetooth® link, Zigbee link, sonic link, optical link, other types of wireless links, or combinations thereof.
One preferred method 61 of wirelessly transmitting data and power is carried out with a radiofrequency link, similar to the link used with radiofrequency identification (RFID) tags. As illustrated in
At step 147 the same RF signal interrogates the energized implantable device 62 to allow the implantable device to sample the desired physiological signal from the subject (such as an EEG signal). At step 149, the implantable device samples the instantaneous EEG signal (or other physiological signal) from the subject.
At step 151, the implantable device 62 then communicates a return RF signal to the external device 64 that is encoded with data that is indicative of the sampled EEG signal. Typically, the return RF signal is a based on the RF signal generated by the external device and includes detectable modifications which indicate the sampled EEG signal. For example, the return signal is typically a backscattering of the RF signal from the external device with the detectable modifications that indicate the sampled EEG signal. Advantageously, such backscattering does not require generation of a separate radiating signal and would not require an internal power source. The return RF signals may also include the identification code of the implanted device so as to identify which device the data is coming from. At step 153, the return RF signal emitted by the internal device 62 is received by the antenna 68, and the RF signal is decoded to extract the sampled EEG signal. The sampled EEG signal may thereafter be stored in a memory of the external device 64. For embodiments in which the method is used to collect data, such data will be stored until accessed by the subject. Typically, such data will be analyzed on a separate device (e.g., physician's computer workstation).
In alternative embodiments, however, in which the external device may comprise software to analyze the data in substantially real-time, the received RF signal with the sampled EEG may be analyzed by the EEG analysis algorithms to estimate the subject's brain state which is typically indicative of the subject's propensity for a neurological event (step 155). The neurological event may be a seizure, migraine headache, episode of depression, tremor, or the like. The estimation of the subject's brain state may cause generation of an output (step 157). The output may be in the form of a control signal to activate a therapeutic device (e.g., implanted in the subject, such as a vagus nerve stimulator, deep brain or cortical stimulator, implanted drug pump, etc.). In other embodiments, the output may be used to activate a user interface on the external device to produce an output communication to the subject. For example, the external device may be used to provide a substantially continuous output or periodic output communication to the subject that indicates their brain state and/or propensity for the neurological event. Such a communication could allow the subject to manually initiate therapy (e.g., wave wand over implanted vagus nerve stimulator, cortical, or deep brain stimulator, take a fast acting AED, etc.) or to make themselves safe.
In preferred embodiments, the return RF signal is transmitted (e.g., backscattered) immediately after sampling of the EEG signal to allow for substantially real-time transfer (and analysis) of the subject's EEG signals. In alternate embodiments, however, the return RF signal may be buffered in an internal memory and the communication transmission to the external device 64 may be delayed by any desired time period and may include the buffered EEG signal and/or a real-time sampled EEG signal. The return RF signal may use the same frequency as the illumination RF signal or it may be a different frequency as the illumination RF signal.
Unlike conventional digital implantable devices that send large packets of stored data with each return RF communication transmission, some embodiments of the methods and devices of the present invention substantially continuously sample physiological signals from the subject and communicate in real-time small amounts of data during each return RF signal communication. Because only small amounts of data (one or a small number of sampled EEG signals from each implantable device 62) are transmitted during each communication, a lower amount of power is consumed and the illumination of the implanted device from the incoming high-frequency RF signal will be sufficient to power the implantable device 62 for a time that is sufficient to allow for sampling of the subject's EEG signal. Consequently, in most embodiments no internal power source, such as a battery, is needed in the implantable device 62—which further reduces the package size of the implantable device 62.
The implantable devices 62 and the external devices 64 of the present invention typically use an electromagnetic field/high frequency communication link to both illuminate the implantable device and enable high data transfer rates. Conventional systems typically have an internally powered implantable device and use a slower communication link (e.g., that is designed for long link access delays) and transmit data out on a non-continuous basis. In contrast, some embodiments of the present invention use a fast access communication link that transmits a smaller bursts of data (e.g., single or small number of EEG sample at a time) on a substantially continuous basis.
The frequencies used to illuminate and transfer data between the implantable devices 62 and external device 64 are typically between 13.56 MHz and 10 GHz, preferably between 402 MHz and 2.4 GHz, more preferably between 900 MHz and 2.4 GHz. While it is possible to use frequencies above 2.4 GHz, Applicants have found that it is preferred to use a frequency below 2.4 GHz in order to limit attenuation effects caused by tissue. As can be appreciated, while the aforementioned frequencies are the preferred frequencies, the present invention is not limited to such frequencies and other frequencies that are higher and lower may also be used. For example, it may be desirable us use the MICS (Medical Implant Communication Service band) that is between 402-405 MHz to facilitate the communication link. In Europe, it may be desirable to use ETSI RFID allocation 869.4-869.65 MHz.
While not illustrated in
If desired, the data signals that are wirelessly transmitted from implantable device 62 may be encrypted prior to transmission to the control module 66. Alternatively, the data signals may be transmitted to the control module 66 as unencrypted data, and at some point prior to the storage of the data signals in the control module 66 or prior to transfer of the data signals to the physician's office, the EEG data may be encrypted so as to help ensure the privacy of the subject data.
Advantageously, the embodiment illustrated in
Housing 1628 is typically in the form of a radially symmetrical, substantially cylindrical body that hermetically seals electronic components 1630 disposed within a cavity 1632. Housing 1628 may be composed of a biocompatible material, such as glass, ceramic, liquid crystal polymer, or other materials that are inert and biocompatible to the human body and able to hermetically seal electronic components. Housing 1628 may have embedded within or disposed thereon one or more x-ray visible markers 33 that allow for x-ray localization of the implantable device. Alternatively, one or more x-ray visible markers may be disposed within the cavity 1632. Cavity 1632 may be filled with an inert gas or liquid, such as an inert helium nitrogen mixture which may also be used to facilitate package leakage testing. Alternatively, it may be desirable to fill the cavity 1632 with a liquid encapsulant (not shown) that hardens around the electronic components. The liquid encapsulant may comprise silicone, urethane, or other similar materials.
While housing 1628 is illustrated as a substantially cylindrical body with the electrodes 1624, 1626 on opposing ends, housing may take any desired shape and the electrodes may be positioned at any position/orientation on the housing 1628. For example, housing 1628 may taper in one direction, be substantially spherical, substantially oval, substantially flat, or the like. Additionally or alternatively, the body may have one or more substantially planar surfaces so as to enhance the conformity to the subject's skull and to prevent rotation of the implantable device 62. While not shown, housing 1628 may optionally include a conductive electromagnetic interference shield (EMI) that is configured to shield the electronic components 1630 in housing 1628. The EMI shield may be disposed on an inner surface of the housing, outer surface of the housing, or impregnated within the housing.
If desired, housing 1628 may optionally comprise an anchoring assembly (not shown) that improves the anchoring of the implantable device 62 to the skull or the layers within the scalp. Such anchoring may be carried out with adhesive, spikes, barbs, protuberances, suture holes, sutures, screws or the like.
In the illustrated embodiment, first electrode 1624 is disposed on a first end of housing 1628 and is in electrical communication with the electronic components 1630 through a hermetic feedthrough 1634. Feedthrough 1634 may be the same material as the first electrode 1624 or it may be composed of a material that has a similar coefficient of thermal expansion as the housing 1628 and/or the first electrode 1624. Feedthrough 1634 may make direct contact with a pad (not shown) on a printed circuit board 1636, or any other type of conventional connection may be used (e.g., solder ball, bond wire, wire lead, or the like) to make an electrical connection to the printed circuit board 1636.
Second electrode 1626 may be spaced from a second, opposing end of the housing 1628 via an elongated coil member 1638. In the illustrated embodiment, the second electrode 1626 typically comprises a protuberance 1639 that is disposed within and attached to a distal end of the coil member 1638. Coil member 1638 acts as an electrical connection between second electrode and the electronic components 1630 disposed within housing 1628.
Coil member 1638 will typically be composed of stainless steel, a high strength alloy such as MP35N, or a combination of materials such as a MP35N outer layer with silver core.
The illustrated embodiment shows that coil member 1638 has a largest lateral dimension (e.g., diameter) that is less than the largest lateral dimension (e.g., diameter) of housing 1628, but in other embodiments, the coil may have the same lateral dimension or larger lateral dimension from housing 1628.
Coil member 1638 may also be used as an antenna to facilitate the wireless transmission of power and data between the implantable device 62 and the external device 64 (or other device). In preferred embodiments, coil member 1638 may be used to receive and transmit radiofrequency signals. In alternative embodiments, however, coil member 1638 may be inductively coupled to an external coil to receive energy from a modulating, alternating magnetic field. Unlike other conventional implantable devices, the RF antenna is disposed outside of the housing 1628 and extends from one end of housing 1628. It should be appreciated, however, that the present invention is not limited to a substantially cylindrical antenna extending from an end of the housing 1628 and various other configurations are possible. For example, it may be desirable to wind the antenna around or within the housing 1628. Furthermore, it may be desirable to use a substantially flat antenna (similar to RFID tags) to facilitate the transmission of power and data. To facilitate implantation, such antennas may be rolled into a cylindrical shape and biased to take the flat shape upon release from the introducer.
While not shown, it may also be desirable to provide a second antenna between the first electrode 1624 and the housing 1628. The second antenna may be used for power and downlink using a first frequency, e.g., 13.56 MHz, while the first antenna may be used for uplink using a second frequency, e.g., 902-928 MHz. In such embodiments, however, the implantable devices would need to have an internal timebase (e.g., oscillator and a frequency synthesizer). For the embodiments that use only a single frequency for the downlink and uplink, an internal timebase or frequency synthesizer is not needed—and the timebase established by the master (e.g., external device 64) can be used.
Coil member 1638 may be in electrical communication with the electronic components 1630 with a hermetic feedthrough 1642 that extends through a via 1644 in housing 1628. Feedthrough 1642 is typically composed of a material that has a coefficient of thermal expansion that is substantially similar to the material of housing 1640. Because the coil member 1638 is outside of the housing 1628 the length of the implantable device 62 will be increased, but the flexible coil will be better exposed to the RF signals and will be allowed to conform to the shape of the subject's skull.
Coil member 1638 is typically disposed outside of the housing 1628 and disposed within an elongate, substantially flexible housing 1640. Compared to the more rigid housing 1628, the flexible housing 1640 is better able to conform to the shape of an outer surface of the subject's skull, more comfortable for the subject and reduces the chance of tissue erosion. Flexible housing 1640 may comprise silicone, polyurethane, or the like In the illustrated embodiment, flexible housing 1640 extends along the entire length of coil member 1638, but in other embodiments, flexible housing 1640 may extend less than or longer than the longitudinal length of coil member 1638. Flexible housing 1640 will typically have a substantially cylindrical shape, but if desired a proximal end 1646 of the cylindrical housing may be enlarged or otherwise shaped to substantially conform to a shape of the housing 1628. The shaped proximal end 1646 may be adhered or otherwise attached to the end of the housing 1640 to improve the hermetic seal of the housing and may reduce any potential sharp edge or transition between the housings 1628, 1640. While
A longitudinal length of flexible housing 1640 and the longitudinal length of the rigid housing 1628 may vary depending on the specific embodiment, but a ratio of the longitudinal length of the flexible housing 1640: the longitudinal length of the more rigid housing 1628 is typically between about 0.5:1 and about 3:1, and preferably between about 1:1 and about 2:1. By having the longitudinal length of the flexible housing longer than the longitudinal length of the rigid housing, advantageously the implantable device will be more comfortable and better able to conform to the outer surface of the subject's skull. In alternative embodiments, it may also be desirable to have a longitudinal length of the rigid housing 1628 be longer than the longitudinal length of the flexible housing 1640, or in any other desired configuration.
Because the implantable devices 62 of the present invention consume a minimal amount of energy and use a high frequency RF coupling to power the device and communicate the EEG signals to the external device, unlike other conventional devices, some of the implantable devices 62 of the present invention will not need a ferrite core to store energy, and the electronic components 1630 of the present invention will typically include aluminum or other MRI-safe material. Consequently, the subject's implanted with the implantable device 62 may safely undergo MRI imaging.
Feedthrough 1642 that is connected to the coil member 1638 extends from the end of coil member 1638 and makes an electrical connection with a lead on the printed circuit board 1636. The feedthrough 1642 works in conjunction with one or more dielectric seals or spacers 52 to hermetically seal the cavity 1632. Similar to above, the cavity 1632 may be filled with an inert gas or an encapsulant. The proximal end 1646 of flexible body 1640 may be coupled to the seals 52 and/or coupled to the conductive body 48.
As shown in the embodiment of
In most embodiments, the implantable devices shown in
While
While
Such implantable devices 62 include an active electrode contact 400 that is in communication with one or more passive electrode contacts 401. The active electrode contact 400 may be used to facilitate monitoring of the physiological signals using the array of active and passive electrode contacts. The arrays of electrode contacts may be arranged in a linear orientation (
A thin or thick filmed microcircuit or a printed circuit board (“PCB”) 416 may be mounted onto an inner surface of the base 402. PCB 416 may have active components 418 (e.g., integrated circuits, ASIC, memory, etc.) and passive components 420 (e.g., resistors, capacitors, etc.) mounted thereto. Leads or bond wires 422 from the active and passive components may be electrically attached to pads on the PCB (not shown) which make electrical connections to leads or bond wires 424 that are attached to the hermetic feedthroughs 413. While not shown in
As noted above, the active contacts may be used in conjunction with one or more passive contacts to form an active implantable device 62 to facilitate monitoring of the subject's physiological signals and to communicate with the external device 64.
As shown in
The first and second electrodes will be used to sample a physiological signal from the subject—typically an EEG signal 1753, and transmit the sampled signal to the electronic components 1630. While it may be possible to record and transmit the analog EEG signal to the external device, the analog EEG signal will typically undergo processing before transmission to the external device 64. The electronic components typically include a printed circuit board that has, among others, an amplifier 1754, one or more filters 1756 (e.g., bandpass, notch, lowpass, and/or highpass) and an analog-to-digital converter 1758. In some embodiments, the processed EEG signals may be sent to a transmit/receive sub-system 60 for wireless transmission to the external device via an antenna (e.g., coil member 1638). Additional electronic components that might be useful in implantable device 62 may be found in U.S. Pat. Nos. 5,193,539, 5,193,540, 5,312,439, 5,324,316, 5,405,367 and 6,051,017.
In some alternative embodiments of the present invention, the electronic components 1630 may include a memory 1764 (e.g., RAM, EEPROM, Flash, etc.) for permanently or temporarily storing or buffering the processed EEG signal. For example, memory 1764 may be used as a buffer to temporarily store the processed EEG signal if there are problems with transmitting the data to the external device. For example, if the external device's power supply is low, the memory in the external device is removed, or if the external device is out of communication range with the implantable device, the EEG signals may be temporarily buffered in memory 1764 and the buffered EEG signals and the current sampled EEG signals may be transmitted to the external device when the problem has been corrected. If there are problems with the transmission of the data from the implantable device, the external device may be configured to provide a warning or other output signal to the subject to inform them to correct the problem. Upon correction of the problems, the implantable device may automatically continue the transfer the temporarily buffered data and the real-time EEG data to the memory in the external device.
The electronic components 1630 may optionally comprise dedicated circuitry and/or a microprocessor 1762 (referred to herein collectively as “microprocessor”) for further processing of the EEG signals prior to transmission to the external device. The microprocessor 1762 may execute EEG analysis software, such as a seizure prediction algorithm, a seizure detection algorithm, safety algorithm, or portions of such algorithms, or portions thereof. For example, in some configurations, the microprocessor may run one or more feature extractors that extract features from the EEG signal that are relevant to the purpose of monitoring. Thus, if the system is being used for diagnosing or monitoring epileptic subjects, the extracted features (either alone or in combination with other features) may be indicative of the subject's susceptibility to or protection from a neurological event (e.g., pro-ictal or contra-ictal). Once the feature(s) are extracted, the microprocessor 1762 may send the extracted feature(s) to the transmit/receive sub-system 1760 for the wireless transmission to the external device and/or store the extracted feature(s) in memory 1764. Because the transmission of the extracted features is likely to include less data than the EEG signal itself, such a configuration will likely reduce the bandwidth requirements for the communication link between the implantable device 62 and the external device 64. Since the extracted features do not add a large amount of data to the data signal, in some embodiments, it may also be desirable to concurrently transmit both the extracted feature and the EEG signal. A detailed discussion of various embodiments of the internal/external placement of such algorithms are described in commonly-owned U.S. patent application Ser. No. 11/322,150, filed Dec. 28, 2005 to Bland et al., the complete disclosure of which is incorporated herein by reference.
While most embodiments of the implantable device 62 are passive and do not need an internal power source or internal clock, in some embodiments, the electronic components 1630 may include a rechargeable or non-rechargeable power supply 1766 and an internal clock (not shown). The rechargeable or non-rechargeable power supply may be a battery, a capacitor, or the like. The rechargeable power supply 1766 may also be in communication with the transmit/receive sub-system 1760 so as to receive power from outside the body by inductive coupling, radiofrequency (RF) coupling, etc. Power supply 1766 will generally be used to provide power to the other components of the implantable device 62. In such embodiments, the implanted device may generate and transmit its own signal with the sampled EEG signal for transmission back to the external device. Consequently, as used herein “transmit” includes both passive transmission of a signal back to the external device (e.g., backscattering of the RF signal) and internal generation of a separate signal for transmission back to the external device.
The EEG data may thereafter be stored in memory 1872, such as a hard drive, RAM, permanent or removable Flash Memory, or the like and/or processed by a microprocessor 1874 or other dedicated circuitry. Microprocessor 1874 may be configured to request that the implantable device perform an impedance check between the first and second electrodes and/or other calibrations prior to EEG recording and/or during predetermined times during the recording period to ensure the proper function of the system.
The EEG data may be transmitted from memory 1872 to microprocessor 1874 where the data may optionally undergo additional processing. For example, if the EEG data is encrypted, it may be decrypted. The microprocessor 1874 may also comprise one or more filters that filter out high-frequency artifacts (e.g., muscle movement artifacts, eye-blink artifacts, chewing, etc.) so as to prevent contamination of the high frequency components of the sampled EEG signals. In some embodiments, the microprocessor may process the EEG data to measure the subject's brain state, detect seizures, predict the onset of a future seizure, generate metrics/measurements of seizure activity, or the like. A more complete description of seizure detection algorithms, seizure prediction algorithms, and related components that may be implemented in the external device 64 may be found in pending, commonly-owned U.S. patent application Ser. Nos. 11/321,897 and 11/321,898, filed on Dec. 28, 2005, to Leyde et al. and DiLorenzo et al., and Ser. No. 12/020,450, filed on Jan. 25, 2008, to Snyder et al., the complete disclosures of which are incorporated herein by reference.
It should be appreciated, however, that in some embodiments some or all of the computing power of the system of the present invention may be performed in a computer system or workstation 1876 that is separate from the system 60, and the external device 64 may simply be used as a data collection device. In such embodiments, the personal computer 1876 may be located at the physician's office or at the subject's home and the EEG data stored in memory 1872 may be uploaded to the personal computer 1876 via a USB interface 1878, removal of the memory (e.g., Flash Memory stick), or other conventional communication protocols, and minimal processing may be performed in the external device 64. In such embodiments, the personal computer 1876 may contain the filters, decryption algorithm, EEG analysis software, such as the contra-ictal algorithm, pro-ictal algorithm, and/or detection algorithm, report generation software, or the like. Some embodiments of the present invention may take advantage of a web-based data monitoring/data transfer system, such as those described in U.S. Pat. Nos. 6,471,645 and 6,824,512, the complete disclosures of which are incorporated herein by reference.
External device 64 may also comprise an RF signal generator 1875 that is configured to generate the RF field for interrogating and optionally powering the implanted devices 62. RF generator 1875 will be under control of the microprocessor 1874 and generate the appropriate RF field to facilitate monitoring and transmission of the sampled EEG signals to the external device.
External device 64 will typically include a user interface 1880 for displaying outputs to the subject and for receiving inputs from the subject. The user interface may comprise outputs such as auditory devices (e.g., speakers) visual devices (e.g., LCD display, LEDs to indicate brain state or propensity to seizure), tactile devices (e.g., vibratory mechanisms), or the like, and inputs, such as a plurality of buttons, a touch screen, and/or a scroll wheel.
The user interface may be adapted to allow the subject to indicate and record certain events. For example, the subject may indicate that medication has been taken, the dosage, the type of medication, meal intake, sleep, drowsiness, occurrence of an aura, occurrence of a neurological event, or the like. Such inputs may be used in conjunction with the recorded EEG data to improve the analysis of the subject's condition and determine the efficacy of the medications taken by the subject.
The LCD display of the user interface 80 may be used to output a variety of different communications to the subject including, status of the device (e.g., memory capacity remaining), battery state of one or more components of system, whether or not the external device 64 is within communication range of the implantable devices 62, brain state indicators (e.g., a warning (e.g., seizure warning), a prediction (e.g., seizure prediction), unknown brain state, safety indication, a recommendation (e.g., “take drugs”), or the like). Of course, it may be desirable to provide an audio output or vibratory output to the subject in addition to or as an alternative to the visual display on the LCD. In other embodiments, the brain state indicators may be separate from the LCD display to as to provide a clear separation between the device status outputs and the brain state indicators. In such embodiments, the external device may comprise different colored LEDs to indicate different brain states. For example, a green LED may indicate a safe brain state, a yellow light may indicate an unknown brain state, and a red light may indicate either a seizure detection or seizure prediction.
As noted above and illustrated in
The external device 64 may also include a medical grade power source 1882 or other conventional power supply that is in communication with at least one other component of external device 64. The power source 1882 may be rechargeable. If the power source 1882 is rechargeable, the power source may optionally have an interface for communication with a charger 1884. While not shown in
In use, one or more of the implantable devices 62 are implanted in the subject. The implanted device 62 is interrogated and powered so that the EEG signals are sampled from the subject's brain. The EEG signals are processed by the implanted device and the processed EEG signals are wirelessly transmitted from the implanted device(s) to an external device. The EEG signals are stored for future or substantially real-time analysis.
The EEG analysis systems shown in
In other embodiments, the signals 103 sampled from the subject may be partially processed in the implantable device 62 before transmitting data to the external device 64 so as to reduce the total amount of data to be transmitted, thereby reducing the power demands of the transmit/receive subsystem 120. Examples include: digitally compressing the signals before transmitting them; encrypting the signals; selecting only a subset of the measured signals for transmission; selecting a limited segment of time and transmitting signals only from that time segment; extracting salient characteristics of the signals, transmitting data representative of those characteristics rather than the signals themselves, and transmitting only the result of classification. Further processing and analysis of the transmitted data may take place in the external device 64.
In yet other embodiments, it may be possible to perform some of the signal processing in the implantable device 62 and some of the signal processing in the external device 64. For example, one or more characteristics from the one or more signals may be extracted with feature extractors in the implantable device 62. Some or all of the extracted characteristics may be transmitted to the external device 64 where the characteristics may be classified to assess the subject's susceptibility for a neurological event. If desired, external device 64 may be tailored to the individual subject. Consequently, the classifier may be adapted to allow for transmission or receipt of only the characteristics from the implantable device 62 that are useful for that individual subject. Advantageously, by performing feature extraction in the implantable device 62 and classification in an external device at least two benefits may be realized. First, the amount of wireless data transmitted from the implantable device 62 to the external device 64 is reduced (versus transmitting pre-processed data). Second, classification, which embodies the decision or judgment component, may be easily reprogrammed or custom tailored to the subject without having to reprogram the implantable device 62.
In yet another embodiment, feature extraction may be performed external to the body. Pre-processed signals (e.g., filtered, amplified, converted to digital) may be transcutaneously transmitted from implantable device 62 to the external device 64 where one or more characteristics are extracted from the one or more signals with feature extractors. Some or all of the extracted characteristics may be transcutaneously transmitted back into the implantable device 62, where a second stage of processing may be performed on the characteristics, such as classifying of the characteristics (and other signals) to characterize the subject's propensity for the onset of a future neurological event. If desired, to improve bandwidth, the classifier may be adapted to allow for transmission or receipt of only the characteristics from the subject communication assembly that are predictive for that individual subject. Advantageously, because feature extractors may be computationally expensive and energy hungry, it may be desirable to have the feature extractors external to the body, where it is easier to provide more processing and larger power sources.
Other details of devices useful for practicing the invention may be found in co-pending and commonly-owned U.S. patent application Ser. No. 12/020,507, filed Jan. 25, 2008, titled “METHODS AND SYSTEMS FOR MEASURING A PATIENT'S SUSCEPTIBILITY TO A SEIZURE,” the disclosure of which is incorporated herein by reference.
One particular advantage of some of the embodiments of the present invention is the ability to provide a substantially continuous, substantially real-time indication to the subject of their neurological condition. In other embodiments of the present invention, the subject may be provided with an indication of their neurological condition on a non-continuous basis. For example, in some embodiments it may be desirable to only provide an output to the subject when there is a change in their condition or if the subject enters a high susceptibility or low susceptibility condition. The ability to inform the subject that they are unlikely to transition to an ictal condition within a period of time will reduce the uncertainty that effects every aspect of their day to day life and opens up the possibility for the subject to perform tasks that most people take for granted.
Such a system would further enable use of novel therapies to prevent the occurrence of the neurological event. Therapies include automatic or manual delivery of anti-epileptic drugs, vagus nerve stimulation, brain stimulation, etc. Some potential therapies are described in commonly-owned U.S. patent application Ser. Nos. 10/889,844 filed Jul. 12, 2004 to DiLorenzo and Ser No. 11/321,898, filed Dec. 28, 2005 to Leyde et al., the complete disclosure of which is incorporated herein by reference.
As noted above, in preferred embodiments, the implantable devices are implanted in a minimally invasive fashion under the subject's scalp 192 and above an outer surface of the skull 191.
While
In a more invasive system shown in
While not shown in
Advantageously, the implantable devices in accordance with some embodiments are able to monitor EEG signals from the subject without the use of burr holes in the skull or implantation within the brain—which significantly reduces the risk of infection for the subject and makes the implantation process easier. While there is some attenuation of the EEG signals and movement artifacts in the signals, because the implantable devices are below the skin, it is believed that there will be much lower impedance than scalp electrodes. Furthermore, having a compact implantable device 62 below the skin reduces common-mode interference signals which can cause a differential signal to appear due to any imbalance in electrode impedance and the skin provides some protection from interference caused by stray electric charges (static).
As shown in
The EEG signal from the subject may be processed (either in the implanted devices and/or in the external device) to estimate the subject's susceptibility to a seizure, step 2206. As described above in
While
While not shown in
While preferred embodiments of the present invention have been shown and described herein, it will be obvious to those skilled in the art that such embodiments are provided by way of example only. Numerous variations, changes, and substitutions will now occur to those skilled in the art without departing from the invention. It should be understood that various alternatives to the embodiments of the invention described herein may be employed in practicing the invention. For example, the present invention also encompasses other more invasive embodiments which may be used to monitor the subject's neurological system.
Alternative embodiments of the implantable device of the present invention may require a neurosurgeon to create a more invasive incision in the subject's scalp. For example, it may be desirable to use a low profile device that is not substantially cylindrical, but instead is substantially planar or concave so as to conform to the curvature of the subject's skull. Such embodiments would likely not be able to be implanted without general anesthesia and may require a surgeon to implant the device.
On the other hand, in some embodiments it may be desirable to be completely non-invasive. Such embodiments include “implantable” devices 62 that are not actually implanted, but instead are “wearable” and may be attached to the outer surface of the skin with adhesive or a bandage so as to maintain contact with the subject's skin. For example, it may be possible to surface mount the device 62 behind the ears, in the scalp, on the forehead, along the jaw, or the like. Because the electrodes are wireless and are such a small size, unlike conventional electrodes, the visual appearance of the electrodes will be minimal.
Furthermore, in some embodiments, it may be desirable to modify the implantable device 62 to provide stimulation to the subject. In such embodiments, the implantable device 62 will include a pulse generator and associated hardware and software for delivering stimulation to the subject through the first and second electrodes 1624, 1626 (or other electrodes coupled to the device. In such embodiments, the external device 64 may include the hardware and software to generate the control signals for delivering the electrical stimulation to the subject.
While preferred embodiments of the present invention have been shown and described herein, it will be obvious to those skilled in the art that such embodiments are provided by way of example only. Numerous variations, changes, and substitutions will now occur to those skilled in the art without departing from the invention. It should be understood that various alternatives to the embodiments of the invention described herein may be employed in practicing the invention. For example, while embodiments described above indicate that power to the implanted devices may be derived wirelessly from an external device and/or from a battery in the implanted device, it should be appreciated that the internal devices may derive or otherwise “scavenge” power from other types of conventional or proprietary assemblies. Such scavenging methods may be used in conjunction with the external power source and/or the internal power source, or it may be used by itself to provide the necessary power for the implanted devices. For example, the implanted devices may include circuitry and other assemblies (e.g., a microgenerator) that derive and store power from subject-based energy sources such as kinetic movement/vibrations (e.g., gross body movements), movement of organs or other bodily fluids (e.g., heart, lungs, blood flow), and thermal sources in the body (e.g., temperature differences and variations across tissue). As can be imagined, such technology could reduce or eliminate the need for recharging of an implanted battery, replacement of a depleted battery, and/or the creation of an external RF field—and would improve the ease of use of the devices by the subjects.
Some embodiments of the monitoring system may include an integral patient diary functionality. The patient diary may be a module in the external device and inputs by the subject may be used to provide secondary inputs to provide background information for the sampled EEG signals. For example, if a seizure is recorded, the seizure diary may provide insight regarding a trigger to the seizure, or the like. The diary may automatically record the time and date of the entry by the subject. Entries by the subject may be a voice recording, or through activation of user inputs on the external device. The diary may be used to indicate the occurrence of an aura, occurrence of a seizure, the consumption of a meal, missed meal, delayed meal, activities being performed, consumption of alcohol, the subject's sleep state (drowsy, going to sleep, waking up, etc.), mental state (e.g., depressed, excited, stressed), intake of their AEDs, medication changes, missed dosage of medication, menstrual cycle, illness, or the like. Thereafter, the subject inputs recorded in the diary may also be used by the physician in assessing the subject's epilepsy state and/or determine the efficacy of the current treatment. Furthermore, the physician may be able to compare the number of seizures logged by the subject to the number of seizures detected by the seizure detection algorithm.
It is intended that the following claims define the scope of the invention and that methods and structures within the scope of these claims and their equivalents be covered thereby.
This application is a continuation of U.S. patent application Ser. No. 12/053,312, filed Mar. 21, 2008 now U.S. Pat. No. 8,036,736 which application claims the benefit of priority to U.S. Provisional Patent Application No. 60/919,364, filed Mar. 21, 2007, the disclosures of which are incorporated by reference herein in their entirety.
| Number | Name | Date | Kind |
|---|---|---|---|
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