Patent Application
20240198103
The present disclosure relates generally to delivery of energy impulses (and/or energy fields) to bodily tissues for therapeutic purposes and, more particularly, to the use of electrical stimulation of the dorsal nasal nerve structure and other sensory and autonomic nerves for treating disorders in a patient, such as headache or pain.
The sphenopalatine ganglion (SPG) (also known as the pterygopalatine ganglion, ganglion pterygopalatinum, Meckel's ganglion, and nasal ganglion) is a nerve ganglion found in the pterygopalatine (sphenopalatine) fossa, close to the sphenopalatine foramen. The SPG has been a clinical target to treat severe headaches since Sluder first described the application of cocaine or alcohol to the vicinity of the SPG, by swabbing through the nostril to the nasopharyngeal mucosa posterior to the middle turbinate. Unfortunately, the SPG swabbing produces only a brief respite from pain, whether by using a cotton swab as originally described by Sluder, or by means of a topical administration device. In addition, injection into the pterygopalatine fossa (PPF) is difficult to perform reliably due to considerable anatomical variability of the patients, with damage to the maxillary artery that lies next to the SPG being not uncommon. Furthermore, the nasal mucosa may slough during needle insertion. Nevertheless, such pharmacological blockade of the SPG has been claimed to be an effective treatment for headaches, asthma, angina, hiccups, epilepsy, glaucoma, neck pain, vascular spasms, facial neuralgias, blindness, low back pain, sciatica, ear ache, menstrual pain, temporomandibular joint dysfunction, and hyperthyroidism.
More recently, anesthetic has been injected into the PPF using modifications of the Sluder methods and devices. Nevertheless, the internal maxillary artery may be at risk no matter where the PPF is punctured.
In addition to the ganglion blockade using anesthetics as described above, ablation (percutaneous radiofrequency, gamma knife, and surgical ganglionectomy) and electrical nerve stimulation have been used to treat pain (especially cluster headaches) originating in, or emanating from, the SPG. The objective of the ablation is to irreversibly damage the SPG to such an extent that it cannot generate the nerve signals that cause pain. This is not a preferred method because ablation would destroy useful neurophysiological functions of the SPG, notwithstanding the pain that the SPG may cause.
In contrast to ablation, the objective of electrical nerve stimulation is to reversibly damage or otherwise inhibit or block activity the SPG. A significant advantage of electrical stimulation over ablation is that it is a reversible procedure. In that regard, SPG neurostimulation resembles the stimulation of other nerves for the treatment of primary headache disorders.
The present disclosure relates generally to delivery of energy impulses (and/or energy fields) to bodily tissues for therapeutic purposes and, more particularly, to the use of electrical stimulation of a dorsal nasal nerve structure, such as a SPG and other sensory and autonomic nerves for treating disorders in a patient, such as headache or pain.
According to one aspect, an implantable neurostimulator includes a lead comprising a plurality of electrodes at a distal end, an implant body comprising electronics for controlling operation of the electrodes and an electrical connector for establishing an electrical connection between the electronics and the electrodes. The implant body comprises a first portion of the electrical connector and the proximal end of the lead comprises a second portion of the electrical connector, the first and second portions of the electrical connector being connectable to establish the electrical connection between the electronics and the electrodes. The lead is configured for initial implantation in the patient and the implant body is configured for subsequent implantation in the patient, and wherein the electrical connector is configured so that the connection of the first and second portions can be performed with the implant body and the lead positioned at a surgical site in the patient.
According to another aspect, alone or in combination with any other aspect, the electrical connector can be a plug-in connector configured so that the electrical connection can be made by pressing together the first and second portions.
According to another aspect, alone or in combination with any other aspect, the first portion of the electrical connector can have a stepped female configuration and the second portion of the electrical connector has a stepped male configuration.
According to another aspect, alone or in combination with any other aspect, the second portion of the connector can be configured for a connection via wires to an external controller. The external controller can be configured to energize the electrodes during implantation in order to obtain feedback for use in positioning the electrodes. The feedback can be feedback indicative of sensing paresthesia induced by the electrodes.
According to another aspect, alone or in combination with any other aspect, the lead can be configured to pass through an 18 gauge surgical needle.
According to another aspect, alone or in combination with any other aspect, the implant body can be configured to pass through a 14 gauge surgical needle.
The implantable neurostimulator can include a remote transducer for providing a wireless signal for powering the stimulator, the remote transducer comprising at least one of a patch, headset, earpiece, extended earpiece, handheld remote controller, headband, and eyeglasses.
According to another aspect, alone or in combination with any other aspect, the implantable neurostimulator can include a remote controller for controlling operation of the remote transducer, the remote controller comprising a foot pedal or a key fob that communicates wirelessly with the remote transducer.
According to another aspect, a method for implanting a two-piece neurostimulator comprising an electrode lead and an implant body connectable with the lead to supply power for energizing the electrodes to apply stimulation therapy includes implanting the lead using a Seldinger technique, implanting the implant body, and connecting the implant body to the lead.
According to another aspect, a method for implanting a two-piece neurostimulator comprising an electrode lead and an implant body connectable with the lead to supply power for energizing the electrodes to apply stimulation therapy to a patient includes attaching a guidewire to the lead, implanting the lead using the guidewire to navigate through the patient's anatomy and position the electrodes at a desired site in the patient, removing the guidewire, leaving the lead implanted, implanting the implant body, and connecting the implant body to the lead.
According to another aspect, a method for implanting a neurostimulator comprising an electrode lead and an implant body for supplying power for energizing the electrodes to apply stimulation therapy to a patient includes attaching a guidewire to the neurostimulator, implanting the stimulator using the guidewire to navigate through the patient's anatomy and position the electrodes at a desired site in the patient, and removing the guidewire, leaving the stimulator.
According to another aspect, a method for implanting a two-piece neurostimulator comprising an electrode lead and an implant body connectable with the lead to supply power for energizing the electrodes to apply stimulation therapy to a patient includes anesthetizing the patient using an anesthesia solution that is sufficient for controlling pain but allows the patient to perceive paresthesia from stimulation, connecting the lead to an external controller that is operable to energize the electrodes to apply stimulation, surgically implanting the lead while applying stimulation via the electrodes, querying the patient for feedback regarding perceived paresthesia during while implanting the lead, using the feedback from the patient to assist in determining a proper position for the lead, securing the lead in the proper position, disconnecting the lead from the external controller, and surgically implanting the implant body and connecting the implant body to the lead.
According to another aspect, alone or in combination with any other aspect, the neurostimulator can be implanted via a gingival-buccal approach, a transoral approach, a trans-nasal a lateral approach through an infratemporal fossa of the patient, or an infrazygomatic approach in which the entry site of the neurostimulator is inferior to the zygoma and anterior to the mandible.
According to another aspect, a method for treating a migraine headache in a patient using an implantable neurostimulator includes programming stimulation parameters into the neurostimulator so that patient does not perceive paresthesia from electrical stimulation of the sphenopalatine ganglion (SPG), implanting the neurostimulator so that a lead of the stimulator having at least one electrode is at a target position proximate to the SPG of the patient, delivering a non-paresthesia stimulation waveform to the at least one electrode based on a therapy parameter set (TPS), the stimulation waveform including a series of pulses configured to excite at least one of A-delta fibers or C-fibers of the SPG of the patient, sensing sensory action potential (SAP) signals of the patient, iterating the steps of delivering the non-paresthesia stimulation waveform and sensing the SAP signals while changing at least one parameter from the TPS, analyzing the SAP signals to obtain SAP activity data associated with the TPS for at least one of an SAP C-fiber component or an SAP A-delta fiber component to obtain a collection of SAP activity data associated with multiple therapy parameter set, selecting one or more parameters for the TPS based on the collection of SAP activity data, programming a pulse generator of the neurostimulator to deliver electrical stimulation to the SPG according to the TPS, activating the neurostimulator so that the pulse generator delivers electrical stimulation to the patient according to the programmed TPS.
The foregoing and other features of the present disclosure will become apparent to those skilled in the art to which the present disclosure relates upon reading the following description with reference to the accompanying drawings, in which:
Unless defined otherwise, all technical and scientific terms used herein have the same meaning as is commonly understood by one of skill in the art to which the present disclosure pertains.
In the context of the present disclosure, the singular forms “a,” “an” and “the” can include the plural forms as well, unless the context clearly indicates otherwise. It will be further understood that the terms “comprises” and/or “comprising,” as used herein, can specify the presence of stated features, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, steps, operations, elements, components, and/or groups thereof.
As used herein, the term “and/or” can include any and all combinations of one or more of the associated listed items.
As used herein, phrases such as “between X and Y” and “between about X and Y” can be interpreted to include X and Y.
As used herein, phrases such as “between about X and Y” can mean “between about X and about Y.”
As used herein, phrases such as “from about X to Y” can mean “from about X to about Y.”
It will be understood that when an element is referred to as being “on,” “attached” to, “connected” to, “coupled” with, “contacting,” etc., another element, it can be directly on, attached to, connected to, coupled with or contacting the other element or intervening elements may also be present. In contrast, when an element is referred to as being, for example, “directly on,” “directly attached” to, “directly connected” to, “directly coupled” with or “directly contacting” another element, there are no intervening elements present. It will also be appreciated by those of skill in the art that references to a structure or feature that is disposed “adjacent” another feature may have portions that overlap or underlie the adjacent feature.
Spatially relative terms, such as “under,” “below,” “lower,” “over,” “upper” and the like, may be used herein for ease of description to describe one element or feature's relationship to another element(s) or feature(s) as illustrated in the figures. It will be understood that the spatially relative terms can encompass different orientations of the apparatus in use or operation in addition to the orientation depicted in the figures. For example, if the apparatus in the figures is inverted, elements described as “under” or “beneath” other elements or features would then be oriented “over” the other elements or features.
It will be understood that, although the terms “first,” “second,” etc. may be used herein to describe various elements, these elements should not be limited by these terms. These terms are only used to distinguish one element from another. Thus, a “first” element discussed below could also be termed a “second” element without departing from the teachings of the present disclosure. The sequence of operations (or steps) is not limited to the order presented in the claims or figures unless specifically indicated otherwise.
As used herein, the term “in communication” can refer to at least a portion of an electrode being adjacent, in the general vicinity, in close proximity, or directly next to and/or directly on (e.g., in physical contact with) a target neural structure, such as a sphenopalatine ganglion (SPG), a sphenopalatine nerve (SPN) (also called the “pterygopalatine nerve”), a vidian nerve (VN) (also called “the nerve of the pterygoid canal”), a greater petrosal nerve (GPN), a lesser petrosal nerve, a deep petrosal nerve (DPN), or a branch thereof (e.g., a nasopalatine nerve, a greater palatine nerve, a lesser palatine nerve, or a superior maxillary nerve). In some instances, the term can mean that at least a portion of an electrode is “in communication” with a target neural structure if application of a therapy signal (e.g., an electrical signal) thereto results in a modulation of neuronal activity to elicit a desired response, such as modulation of a nerve signal (e.g., an action potential or electrical impulse) generated in, or transmitted through, the target neural structure. In such instances, it can be understood that the electrode (or a portion thereof) is in electrical communication with the target neural structure.
A “dorsal nasal nerve structure” includes a SPG, a maxillary nerve, DPN, GPN, VN, nasopalatine nerve, superior posterior lateral nasal branches from the SPG, lesser palatine nerve, greater palatine nerve, and/or an inferior posterior lateral nasal branch from the greater palatine nerve. As used herein with respect to the dorsal nasal nerve structure, the term “electrical communication” refers to the ability of an electric field generated by an electrode to be transferred to the dorsal nasal nerve structure and/or to have a neuromodulatory effect on the dorsal nasal nerve structure. The electrode can be positioned in direct electrical communication with the dorsal nasal nerve structure such that electrode is adjacent to the dorsal nasal nerve structure to directly stimulate the dorsal nasal nerve structure. Such direct electrical stimulation is in contrast to an electrode being placed adjacent to a site distal or proximal to the dorsal nasal nerve structure and thus directly stimulating such distal or proximal sites and indirectly stimulating the dorsal nasal nerve structure. For example, placing an electrode in direct electrical communication with a dorsal nasal nerve structure means that the electrode is not placed adjacent to distal or proximal sites that do or do not innervate the dorsal nasal nerve structure such as, for example, the trigeminal nerve, a branch of the trigeminal nerve, a trigeminal ganglion or the vagus nerve.
As used herein, the term “electrical communication” with respect to a neurostimulator can refer to the ability of an electric field generated by an electrode or electrode array to be transferred, and/or to have a neuromodulatory effect, within and/or on a nerve, neuron, or fiber of a target neural structure.
As used herein, the term “subject” can be used interchangeably with the term “patient” and refer to any warm-blooded organism including, but not limited to, human beings, pigs, rats, mice, dogs, goats, sheep, horses, monkeys, apes, rabbits, cattle, etc.
As used herein, the terms “modulate” or “modulating” with reference to activity of a target neural structure can refer to causing a change in neuronal activity, chemistry and/or metabolism. The change can refer to an increase, decrease, or even a change in a pattern of neuronal activity. The terms may refer to either excitatory or inhibitory stimulation, or a combination thereof, and may be at least electrical, magnetic, optical or chemical, or a combination of two or more of these. The terms “modulate” or “modulating” can also be used to refer to a masking, altering, overriding, or restoring of neuronal activity.
As used herein, the terms “substantially blocked” or “substantially block” when used with reference to activity of a target neural structure can refer to a complete (e.g., 100%) or partial inhibition (e.g., less than 100%, such as about 90%, about 80%, about 70%, about 60%, or less than about 50%) of nerve conduction therethrough. For example, the terms “block”, “blocking”, and “blockade” can refer to the disruption, modulation, and/or inhibition of nerve impulse transmissions through a target neural structure.
As used herein, the term “activity” when used with reference to a target neural structure can, in some instances, refer to the ability of a nerve, neuron, or fiber to conduct, propagate, and/or generate an action potential. In other instances, the term can refer to the frequency at which a nerve or neuron is conducting, propagating, and/or generating one or more action potentials at a given moment in time. In further instances, the term can refer to the frequency at which a nerve or neuron is conducting, propagating, and/or generating one or more action potentials over a given period of time (e.g., seconds, minutes, hours, days, etc.).
As used herein, the terms “prevent” or “preventing” when used with reference to a medical condition (e.g., pain or headache) can refer to stopping a medical condition from occurring, or taking advance measures against the possibility or probability that a medical condition will happen or occur. In some instances, the terms can refer to an action or actions taken to decrease the chance that a subject will contract, develop, or suffer from a medical condition.
As used herein, the terms “suppress” or “suppressing” when used with reference to a medical condition can refer to refer to any quantitatively or qualitatively measurable or observable reduction or attenuation in a medical condition (e.g., a sign or symptom associated with the medical condition).
As used herein, the term “medical condition” can refer to any condition, state, or disease that is characterized, at least in part, by a disruption in sensory signals passing through or associated with the autonomic nervous system (ANS). Non-limiting examples of medical conditions can include pain, autonomic disorders, and neurological disorders. Other examples of medical conditions treatable by the present disclosure can include those disclosed in U.S. Pat. No. 6,526,318 to Ansarinia, U.S. Pat. No. 9,220,524 to Boling et al., U.S. patent application Ser. No. 13/746,038 to Caparso, U.S. patent application Ser. No. 13/917,917 to Goodman et al., U.S. patent application Ser. No. 13/917,953 to Goodman et al., and U.S. patent application Ser. No. 14/093,094 to Pless et al. For example, medical conditions can include headache pain. Headache pain can result from migraine headaches, including migraine headaches with aura, migraine headaches without aura, menstrual migraines, migraine variants, atypical migraines, complicated migraines, hemiplegic migraines, transformed migraines, and chronic daily migraines; episodic tension headaches; chronic tension headaches; analgesic rebound headaches; episodic cluster headaches; chronic cluster headaches; cluster variants; chronic paroxysmal hemicrania; hemicrania continua; post-traumatic headache; post-traumatic neck pain; post-herpetic neuralgia involving the head or face; pain from spine fracture secondary to osteoporosis; arthritis pain in the spine, headache related to cerebrovascular disease and stroke; headache due to vascular disorder; reflex sympathetic dystrophy, cervicalgia (which may be due to various causes, including, but not limited to, muscular, discogenic, or degenerative, including arthritic, posturally related, or metastatic); glossodynia, carotidynia; cricoidynia; otalgia due to middle ear lesion; gastric pain; sciatica; maxillary neuralgia; laryngeal pain, myalgia of neck muscles; trigeminal neuralgia (sometimes also termed tic douloureux); post-lumbar puncture headache; low cerebro-spinal fluid pressure headache; temporomandibular joint disorder; atypical facial pain; ciliary neuralgia; paratrigeminal neuralgia (sometimes also termed Raeder's syndrome); petrosal neuralgia; Eagle's syndrome; idiopathic intracranial hypertension; orofacial pain; myofascial pain syndrome involving the head, neck, and shoulder; chronic migraneous neuralgia, cervical headache; paratrigeminal paralysis; sphenopalatine ganglion neuralgia (sometimes also termed lower-half headache, lower facial neuralgia syndrome, Sluder's neuralgia, and Sluder's syndrome); carotidynia; Vidian neuralgia; and causalgia; or a combination of the above
As used herein, the term “medical condition mediated by autonomic or neurological dysfunction” can refer to any condition, state, or disease that is characterized, at least in part, by a disruption in nerve signals (e.g., action potentials or electrical impulses) passing through or associated with the autonomic nervous system (ANS). Such medical conditions can result from, be caused by (e.g., directly or indirectly), or otherwise be associated with autonomic or neurological dysfunction. Non-limiting examples of medical conditions mediated by autonomic or neurological dysfunction are provided below.
As used herein, the terms “treat” or “treating” can refer to therapeutically regulating, preventing, improving, alleviating the symptoms of, and/or reducing the effects of a medical condition (e.g., mediated by autonomic or neurological dysfunction). As such, treatment also includes situations where a medical condition, or at least symptoms associated therewith, is completely inhibited, e.g., prevented from happening or stopped (e.g., terminated) such that the subject no longer suffers from the medical condition, or at least the symptom(s) that characterize the medical condition.
A brief discussion of the pertinent neurophysiology is provided to assist the reader with understanding certain aspects of the present disclosure.
The autonomic nervous system innervates numerous pathways within the human body and consists of two divisions: the sympathetic and the parasympathetic nervous systems. The sympathetic and parasympathetic nervous systems are antagonistic in their action, balancing the other system's effects within the body. The sympathetic nervous system (SNS) usually initiates activity within the body, preparing the body for action, while the parasympathetic nervous system (PNS) primarily counteracts the effects of the SNS.
The sphenopalatine ganglia 10 (
The parasympathetic activity of the SPG 10 is mediated through the greater petrosal nerve (not shown), while the sympathetic activity of the SPG is mediated through the deep petrosal nerve (not shown), which is essentially an extension of the cervical sympathetic chain (not shown). Sensory sensations generated by or transmitted through the SPG 10 include, but are not limited to, sensations to the upper teeth, feelings of foreign bodies in the throat, and persistent itching of the ear. The SPG 10 transmits sensory information, including pain, to the trigeminal system via the maxillary division and ophthalmic division (not shown).
The present disclosure relates generally to a system and apparatus for implementing neuromodulatory methods. More particularly, the present disclosure relates generally to a system and apparatus for implementing neuromodulatory methods for treating medical conditions by stimulation of a target neural structure. As discussed in more detail below, the system and apparatus can be used to implement methods for suppressing or preventing medical conditions by disrupting sensory signals passing through the ANS, such as pain signals. The abnormal regulation of pain or autonomic pathways, which may be a feature of the medical conditions disclosed herein, can cause excitation, loss of inhibition, suppression, or loss of excitation of these pathways. Thus, in some instances, the system and apparatus can be used to implement methods for applying one or more electrical signals to a target neural structure in order to modulate the transmission of sensory signals and stimulate or block the autonomic pathways passing through the target neural structure to reduce or eliminate one or more symptoms or signs associated with a medical condition. In other instances, the application of one or more electrical signals to a target neural structure can modulate the transmission of sensory signals other than pain responsible for provoking or aggravating other undesirable sensations or conditions, such as nausea, bladder disorders, sleep disorders or abnormal metabolic states.
According to one aspect, the present disclosure relates to a system 16 (
The neurostimulator 18 can be sized and dimensioned for injection or insertion into a PPF 14 of a patient. The neurostimulator 18 can comprise electronic circuitry (not shown), one or more electrodes (not shown) that is/are driven by the circuitry, and one or more transmit coils, radiators, or PCB antennas (not shown). The electronic circuitry of the neurostimulator is programmed to receive and transmit data (e.g., stimulation parameters) and/or power from outside the body. In some instances, the electronic circuitry can be encapsulated by an insulative, biocompatible resin. The neurostimulator 18 can be entirely or partly formed from a flexible, biocompatible polymer. In some instances, the electronic circuitry can include a programmable memory for storing at least one set of stimulation and control parameters. In other instances, the neurostimulator 18 can include a power source (not shown) and/or power storage device (not shown). Possible power options can include, but are not limited to, various wireless charging mechanisms, such as an external power source coupled to the neurostimulator via an RF link using coils or radiators, a self-contained power source utilizing any means of generation or storage of energy (e.g., a primary battery, a rechargeable battery, such as a lithium ion battery, a button or coin cell battery, an electrolytic capacitor, or a super- or ultra-capacitor), and, if the self-contained power source is rechargeable, a mechanism for recharging the power source (e.g., an RF link). In some instances, the system 16 can include a retractable power cable (not shown) that can be selectively connected to the power source and/or power storage device.
The neurostimulator 18 can be sized and dimensioned for injection or insertion into the PPF 14 via an elongated, hollow, tubular delivery device 26 (
According to another aspect, referring to
In another aspect, the system 16 can include a personal electronic device 22 that is in electrical communication (e.g., wireless communication) with the remote transducer 20. Examples of personal electronic devices 22 can include smart phones and tablets, although it will be appreciated that personal computers (PCs) may also be included. In some instances, the personal electronic device 22 can include software programmed to control one or more stimulation and/or control parameters associated with the neurostimulator. Additionally, or optionally, the software comprising the personal electronic device 22 can be programmed to store patient therapy data, such as diary questions and patient incentive information, and/or promote patient-to-patient interaction. For instance, the personal electric device 22 can be programmed to include an electronic leader board where patients are ranked against other patients based on certain usage goals. The personal electronic device can also be programmed to interact with an incentive program for patients to earn “points” for compliance (e.g. activating the device once every day for 20 minutes) so that a manufacturer could study new therapies or gather product data. The personal electronic device 22 can also include software programmed to access remote data sources (e.g., Internet websites), query certain data, and then provide stimulation instructions to the system 16 based on the queried data. For example, the personal electronic device 22 can access a website that provides weather-related information (e.g., Accuweather) and then, based on information obtained from the website, provide predictive information and/or stimulation instructions for a particular medical condition (e.g., migraine). In another example, the personal electronic device 22 can also include software programmed to provide the neurostimulator 18 with customizable or patient-triggered alerts, e.g., indicating stimulation periods and the duration of each period, after a desired period of time (e.g., 1.5 hours) after sleep onset, or after consumption of food or water. In some instances, the personal electronic device 22 can be operated manually by the patient or a caregiver.
In another aspect, the system 16 can additionally or optionally comprise a programming device 24 that is in electrical communication (e.g., wireless communication) with the remote transducer 20. The programming device 24 can be configured and programmed to deliver stimulation and/or control instructions to the remote transducer 20. In one example, the programming device 24 can be configured as a dedicated, smart phone-sized unit. In another example, the programming device 24 can be configured as a smart phone accessory dongle. In some instances, the programming device 24 can be operated manually by the patient or a caregiver. In other instances, the programming device 24 can be battery powered and/or directly powered, e.g., by an AC source. If powered by rechargeable batteries, a battery charger may be an accessory to the programming device 24.
In another aspect, the system 16 can include one or more sensors (not shown) to permit open-loop or closed-loop control. In an open-loop system, for example, the system 16 can include one or more sensors such that a patient can manage (e.g., prophylactically) treatment of a medical condition based on feedback (e.g., detected signals) from the sensor(s). Such detected signals can be indicative of the onset of a medical condition, such as an increase in blood flow, skin resistance, temperature, etc. Upon noticing the signal(s), the patient can then trigger or activate the neurostimulator 18 to prevent or mitigate onset of the medical condition.
In another aspect, the system 16 can include one or more sensors to permit closed-loop control by, for example, automatically responding (e.g., by activation of the neurostimulator 18) in response to a sensed environmental parameter and/or a sensed physiological parameter, or a related symptom or sign, indicative of the extent and/or presence of a medical condition. In one example, the sensor(s) can detect an environmental parameter, such as barometric pressure, ambient temperature, humidity, etc. In another example, the sensor(s) can detect a physiological parameter, or a related symptom or sign, indicative of the extent and/or presence of a medical condition, non-limiting examples of which include skin resistance, blood flow, blood pressure, a chemical moiety, nerve activity (e.g., electrical activity), protein concentrations, electrochemical gradients, hormones (e.g., cortisol), electrolytes, markers of locomotor activity, and cardiac markers (e.g., EKG RR intervals). Sensors used as part of a closed-loop or open-loop system can be placed at any appropriate anatomical location on a subject, including a skin surface, an intra-oral cavity, a mucosal surface, or at a subcutaneous location. Examples of sensors and feedback control techniques that may be employed as part of the present disclosure are disclosed in U.S. Pat. No. 5,716,377.
From the above, it will be appreciated that the system 16 includes an implantable portion or part comprising the neurostimulator 18 and an external portion or part comprising the remote transducer 20 for powering and/or communicating with the neurostimulator. The system 16 can be configured for active or passive stimulation. In an active stimulation configuration, the neurostimulator includes hardware configured to store at least some parameters/settings, and to control activation of the electrodes in order to apply stimulation therapy according to the stored parameters/settings. In a passive stimulation configuration, the neurostimulator is configured via hardware to activate the electrodes in a predetermined manner in response to the excitation signal received form the remote transducer.
Referring to the block diagram of
The power transmitter portion 50 transmits power using wireless power transfer technologies mated to the power portion 30 of the neurostimulator 18. The power transmitter portion 50 includes a transmission element, such as a coil or antenna, for generating a wireless power transfer signal, such as an RF power transfer signal. The power transmitter portion 50 can therefore be configured to transmit power to the neurostimulator 18 via wireless power transfer technologies, such as inductive coupling, inductive resonate magnetic coupling, capacitive coupling, near-field coupling, mid-field coupling, far-field coupling, microwave power, ultrasonic/acoustic power, and light power.
One particular wireless power transfer technology that can be implemented in the remote transducer 20 is microwave RF power transfer technology. Microwave RF power transfer operates at 2-10 GHz and is highly efficient and can be implemented using a comparatively small form factor antenna. Additionally, microwave power transfer does not pose any directivity issues, so the orientation and position of the remote transducer relative to the neurostimulator 18 can be more generalized.
The telemetry portion 52 communicates via an RF communication protocol mated to the telemetry portion 32 of the neurostimulator 18. The telemetry portion 52 can therefore be configured to communicate via can communicate via any appropriate radio frequency communication protocol.
The electronics portion 54 can be configured to perform control functions, processing functions, power management functions, and telemetry functions to control communications with the neurostimulator 18 and external devices, such as a personal electronic device 22 via Bluetooth, Wi-Fi, etc.
The battery portion 56 can be detachable for swapping and prolonged usage. A swappable battery portion 56 can be disposable or rechargeable. An example battery portion is a rechargeable lithium-ion battery.
The wireless communication link portion 58 performs the communication with the neurostimulator 18 under the direction of the telemetry control performed by the electronics portion 54. The wireless communication link portion 58 can, for example, include a Bluetooth radio and/or a Wi-Fi radio.
Also, referring to the block diagram of
The power portion 30 provides electrical power to the neurostimulator components that require it. The power portion 30 can be any of the following, individually or in combination: wireless power, battery power, and charge banks. When the power portion 30 includes wireless power, it is configured to receive power from the remote transducer via wireless power transfer technologies, such as inductive coupling, resonate inductive coupling, capacitive coupling, near-field coupling, mid-field coupling, far-field coupling, microwave power, ultrasonic/acoustic power, and light power. When the power portion 30 includes battery power, the batteries can be disposable batteries, such as nickel-cadmium batteries or rechargeable batteries, such as lithium-ion batteries. When the power portion 30 includes charge banks, the charge banks can include capacitors, inductors, and super-capacitors, which can be used on a standalone basis or in combination with the battery and/or wireless power.
The telemetry portion 32 can communicate via any radiofrequency (RF) technology for communicating with the remote transducer 20.
The sensor portion 34 can be any sensor used to sense the sphenopalatine ganglion (SPG) nerve bundle for closed loop feedback control.
The electronics portion 36 can be configured to perform control functions, processing functions, power management, telemetry control, and stimulation control.
The electrodes portion is the portion that establishes electrical contact with the sphenopalatine ganglion (SPG) nerve bundle to deliver the stimulation current to the SPG nerve bundle.
Referring to the diagram of
The remote transducer 20 can have the same general configuration as those described above with reference to
According to the passive neurostimulator configuration of
The design/configuration of the neurostimulator 18 can vary. Example configurations are shown in
According to one aspect, the neurostimulator 18 can have a single component configuration. Referring to
The implant body 52 includes the electronic components necessary to perform the various functions for applying stimulation therapy via the electrodes 60. These components can include, for example, application specific integrated circuits (ASICs), custom field programmable gate array (FPGA) chips, a system on a chip (SoC), an integrated circuit (IC) with additional components assembled in a ceramic package, or a combination thereof. In one particular configuration, the implant body 52 can include an application specific integrated circuit (ASIC) with discrete components, such as antennas/coils, capacitors, resistors, etc., for power transmission, distribution, and control. The lead 54 includes a lead body 62 and lead wires 64 that extend through the lead body and electrically connect the electronics of the implant body 52 to the electrodes 60. The lead wires 64 can extend through the lead body 62, for example, by passing through an inner lumen of the lead (i.e., the lead body 62 can have a tubular construction) or by being embedded within the lead body material (e.g., the lead body can have a solid construction).
The lead body 62 and lead wires 64 have a configuration and material construction selected such that the lead 54 can be both flexible and deformable. This bending is shown by way of example in dashed lines in the figures. As a result, the lead 54 can be bent or otherwise physically manipulated to a shape that is maintained once released. For example, the deformable characteristics of the lead 54 can be created through the metal material used to form the lead wires 64. The material used to construct the lead body 62 can be a flexible, conforming material, such as a soft plastic or polymer, that adopts the shape to which the metal lead wires 64 are bent or otherwise deformed. The metal used to form the lead wires 64, can be selected to have a ductility such that the lead wires can maintain the shape into which they are bent or otherwise deformed. The lead wires 64 can, for example, be constructed of solid copper wire (as opposed to stranded wire).
The lead 54 can be bent to follow the anatomy of the patient, allowing the electrodes 60 to be positioned at a desired position and orientation relative to the SPG. This also allows the implant body 52 to be positioned in a location that is least intrusive to the patient in terms of discomfort and/or visibility (e.g., externally visible lumps), if applicable. The lead 54, following or conforming to the patient anatomy, can help maintain the entire stimulator 50 in the desired implanted position/orientation.
According to another aspect, the neurostimulator 18 can have a multiple component configuration. Referring to
The implant body 102 includes the electronic components necessary to perform the various functions for applying stimulation therapy via the electrodes 110. The implant body 102 can include an application specific integrated circuit (ASIC) with discrete components, such as antennas/coils, capacitors, resistors, etc., for power transmission, distribution, and control. The lead 104 includes a lead body 112 and lead wires 114 that extend through the lead body and electrically connect the electronics of the implant body 102 to the electrodes 110. The lead wires 114 can extend through the lead body 112, for example, by passing through an inner lumen of the lead (i.e., the lead body 112 can have a tubular construction) or by being embedded within the lead body material (e.g., the lead body can have a tubular or solid construction).
The neurostimulator 100 includes a connector 116 for facilitating the detachable connection between the implant body 102 and the lead 104. Referring to
The first portion 120 includes electrical contacts 122 that engage corresponding electrical contacts 132 on the second portion 130 when the first and second portions of the connector 116 are interconnected with each other. The electrical contacts 122 of the first portion 120 are electrically connected to the electronics of the implant body 102. The electrical contacts 132 of the second portion 130 are electrically connected to the electrodes 110 via the lead wires 114. The number of electrical contacts 122, 132 provided on the first and second portions 120, 130 can correspond to the number of electrodes on the lead 104. For instance, in the example configuration of the stimulator 100 illustrated in
The lead body 112 and lead wires 114 can have a configuration and material construction selected such that the lead 104 can be both flexible and deformable. As a result, the lead 104 can be bent or otherwise physically manipulated to a shape that is maintained once released. For example, the deformable characteristics of the lead 104 can be created through the metal material used to form the lead wires 114. The material used to construct the lead body 112 can be a flexible, conforming material, such as a soft plastic or polymer, that adopts the shape to which the metal lead wires 114 are bent or otherwise deformed. The metal used to form the lead wires 114, can be selected to have a ductility such that the lead wires maintain the shape into which they are bent or otherwise deformed. The lead wires 114 can, for example, be constructed of solid copper wire (as opposed to stranded wire).
The lead 104 can be bent to follow the anatomy of the patient, allowing the electrodes 110 to be positioned at a desired position and orientation relative to the SPG. This also allows the implant body 102 to be positioned in a location that is least intrusive to the patient in terms of discomfort and/or visibility (e.g., externally visible lumps), if applicable. The lead 104, following or conforming to the patient anatomy, can help maintain the entire neurostimulator 100 in the desired implanted position/orientation.
The two-piece configuration of the neurostimulator 100 can allow for implanting the lead 104 separately from the implant body 102. Since the lead 104 can be configured to have a diameter that is smaller than the implant body 102, implanting the lead separately can allow for it to be delivered using a smaller diameter device, such as a surgical needle. The implant body 102, having a larger diameter, can be delivered with a larger diameter device/needle. For instance, in one example configuration, the implant body 102 can be configured for delivery via a 14 gauge needle and the lead 104 can be configured for delivery via an 18 gauge needle. Delivering the lead 104 with a smaller needle can offer greater dexterity and can reduce the invasiveness of the procedure, and the discomfort and pain felt by the patient.
Additionally, the connector 116 can facilitate connecting the lead 104 to an external device, which enables actuation of the electrodes 110 without requiring the use of the remote transducer 20. Because of this, an external device, such as a controller, can be wired directly to the lead 104 and used to apply stimulation via the electrodes 110 in order to assist in finding the proper placement of the lead 104.
According to another aspect, the neurostimulator 18 can be configured to be used in conjunction with a guidewire for delivering the neurostimulator during implantation without requiring a separate implantation device, such as a needle or tube. An example of this is shown in
The implant body 152 of the neurostimulator 150 can have a flattened configuration so that the guidewire 160 can pass over and extend along the lead 154 with minimal bending. Because of this, the guidewire 160 can be used to deliver the lead 154 alone (two-piece neurostimulator configuration) or along with the implant body 152 (one or two-piece neruostimulator configuration). Holders 162 in the form of loops or straps can be used to help secure the guidewire 160 to the lead 154.
As shown in
Regardless of the particular configuration of the neurostimulator 18 and the methods used to implant the device, the wireless power transfer from the remote transducer 20 to the neurostimulator has several characteristics that can be the same or similar across the platform. For example, antenna excitation power can be ≤1 watt, and the Equivalent Isotropically Radiated Power (EIRP) can be ≤4 watts (W), per FCC guidelines. The remote transducer 20 can generate a 3D electric field for a power transfer of 25-35 milliwatts (mW) between the transducer and stimulator coils/antennas. The frequency of the wireless power transfer can be selected from the frequencies set forth in the following table:
Current magnetic wireless power transfer technologies utilize inductive resonant magnetic coupling (126 kHz), which is effective, but is less efficient, can make coil form factors difficult to optimize, and can produce issues with coil directivity, alignment, and orientation, which can make coupling difficult. Microwave RF power transfer technology, which is highly efficient, has a small form factor antenna, and does not exhibit directivity issues, can also be implemented.
For the neurostimulator 18, in order to maintain the small diameter, needle-based implantation capability, the antenna can have a printed circuit board (PCB) configuration, a ferrite rod configuration, a helical coil configuration, or a circular loop configuration.
The remote transducer 20 is not limited to a hand-held form factor. The implant body/lead configuration of the neurostimulator allows the electrodes 38 to be positioned at a desired location in the patient and the implant body can be positioned and oriented with the antenna close to the skin surface in a position selected to optimize alignment with, and signal reception from, the remote transducer 20. Because of this, the remote transducer 20 can have one of a variety of form factors, and the neurostimulator 18 can be configured to position the antenna for receiving a stimulation control signal from the particular form factor that is chosen. Examples of some of these form factors are illustrated in
Referring to
Another form factor of the remote transducer 20 can comprise a headset 210, two of which are illustrated in
Referring to
Referring to
Referring to
Referring to
Referring to
Operation of the remote transducer 20 can be initiated via the transducer itself, e.g., via buttons or switches on the transducer, via a smart device, such as a smartphone, or via a remote control device. For example, operation of the remote transducer 20 can be initiated by remote control devices, such as a foot pedal 270 (
There are several surgical approaches that may be used to deliver a neurostimulator 18 into the PPF 14 via the delivery device 26 (see
The SPG 10 can be localized using at least one scanning apparatus, such as a CT scan or fluoroscope. Further details of the localization procedure are disclosed in U.S. Pat. No. 6,526,318 to Ansarinia.
The entry point for the insertion of the delivery device 26 can be located in the coronoid notch between the condylar and coronoid processes of the ramus of the mandible. Once the entry point is localized, the skin overlying the entry point can be shaved and prepared with antiseptic solution. A 25-gauge needle can be used to inject a subcutaneous local anesthetic (e.g., 2 cc of 2% lidocaine) into the skin and subcutaneous tissues overlying the entry point. In addition to the local anesthetic, the patient may be given intravenous sedation and prophylactic antibiotics prior to commencement of the implantation procedure, if desired. In this manner, the patient can receive the local anesthetic for pain and comfort while still being to detect paresthesia so that they can assist by giving feedback during lead delivery and placement.
The delivery device 26 can be inserted at the entry point and advanced between the coronoid process and the condylar process of the ramus of the mandible towards the PPF 14 (
In one example, the neurostimulator 18 can be implanted in the patient without penetrating the cranium of the patient. In another example, the neurostimulator 18 can be implanted in the patient without penetrating the palate and/or without entering the nasal cavity of the patient.
The neurostimulator 18 is configured so that it can be implanted using a standard surgical needle. For the one-piece stimulator 50 of
For the two-piece stimulator 100 of
Additionally, since the implant body 102 can be implanted with less precision and closer to the skin surface, its delivery is better suited for the larger 18 gauge needle. Since the implant body 102 can be implanted closer to the surface, and since the lead 104 is flexible/bendable, the implant body can be positioned, oriented, and aligned in an ideal manner for communicating with the remote transducer 20. This position and orientation can be tailored to complement the chosen form factor of the remote transducer 20 (see
The neurostimulator 18, or portions thereof, can also be implanted using a technique known as a Seldinger technique. According to this technique, the desired tissue is punctured with a sharp hollow needle called a trocar, with ultrasound/image guidance if necessary. A round-tipped guidewire is then advanced through the lumen of the trocar and through the tissue to a desired location relative to the SPG, and the trocar is withdrawn. A tube, such as a sheath, cannula, etc., is then passed over the guidewire into the patient to the desired location. Once the tube is positioned, the guidewire is withdrawn. The neurostimulator 18 can then be delivered to the SPG through the tube, and the electrodes 38 can be positioned at the desired location. Once the neurostimulator 18 is secured at the desired position and location, the tube can be removed, leaving the neurostimulator in place.
The Seldinger technique can be advantageous for implantation of the two-piece stimulator 100 of
With regard to the stimulator 150 of
The delivery and implantation methods described herein can also be combined. For example, for a two-piece configuration of the stimulator 150, the lead 154 can be delivered via the guidewire 160, and the implant body 152 can be delivered using a needle. As another example, for a two-piece configuration of the stimulator 150, the lead 154 can be delivered using the Seldinger technique, and the implant body 152 can be delivered using a needle.
Once implanted, the remote transducer 20 can be brought into contact (or close contact) with the head of the patient so that the remote transducer is within close proximity (which can range from approximately 2 centimeters to approximately 10 meters) to the implanted neurostimulator 18. Where the remote transducer 20 comprises a patch, for example, a skin-contacting surface of the patch can be brought into direct contact with the cheek of the patient, immediately adjacent the location of the implanted neurostimulator 18.
The remote transducer 20 can be activated (
In one example neurostimulation method, the neurostimulator 18 can be used to treat a migraine headache in a manner such that the therapy is transparent to the patient. To do so, stimulation parameters can be programmed into the neurostimulator 18 so that patient does not feel the paresthesia that can accompany neurostimulation. According to this method, a patient can be treated for a headache by controlling non-paresthesia stimulation of autonomic system, such as the SPG by implanting lead having at least one electrode at a target position proximate to the SPG of the patient. A non-paresthesia stimulation waveform can be delivered to the at least one electrode based on a therapy parameter set (TPS). The stimulation waveform can include a series of pulses configured to excite at least one of A-delta fibers or C-fibers of the SPG of the patient. Sensory action potential (SAP) signals can also be sensed. The method can include iteratively delivering the non-paresthesia waveform and sensing the SAP signals while changing at least one parameter from the TPS. The SAP signals can be analyzed to obtain SAP activity data associated with the TPS for at least one of an SAP C-fiber component or an SAP A-delta fiber component. Through this analysis, a collection of SAP activity data associated with multiple therapy parameter set can be obtained. One or more parameters for the TPS can be selected based on the collection of SAP activity data. The pulse generator of the neurostimulator can be programmed to deliver stimulation to the SPG according to the TPS, and the neurostimulator can be activated so that the pulse generator delivers electrical stimulation to the patient according to the programmed TPS.
From the above description of the present disclosure, those skilled in the art will perceive improvements, changes and modifications. Such improvements, changes, and modifications are within the skill of those in the art and are intended to be covered by the appended claims. All patents, patent applications, and publication cited herein are incorporated by reference in their entirety.
This application is a continuation of U.S. Ser. No. 17/327,442, filed May 21, 2021, which is a continuation of U.S. Ser. No. 16/233,611, filed Dec. 27, 2018, which claims benefit of U.S. Provisional Ser. No. 62/611,254, filed Dec. 28, 2017, the entire contents of which are incorporated herein by reference.
| Number | Date | Country | |
|---|---|---|---|
| 62611254 | Dec 2017 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 17327442 | May 2021 | US |
| Child | 18591326 | US | |
| Parent | 16233611 | Dec 2018 | US |
| Child | 17327442 | US |
