Patent Grant
11123569
The present invention relates to neurostimulation treatment systems and associated devices, as well as methods of treatment, implantation and configuration of such treatment systems.
Treatments with implantable neurostimulation systems have become increasingly common in recent years. While such systems have shown promise in treating a number of conditions, effectiveness of treatment may vary considerably between patients. A number of factors may lead to the very different outcomes that patients experience, and viability of treatment can be difficult to determine before implantation. For example, stimulation systems often make use of an array of electrodes to treat one or more target nerve structures. The electrodes are often mounted together on a multi-electrode lead, and the lead implanted in tissue of the patient at a position that is intended to result in electrical coupling of the electrode to the target nerve structure, typically with at least a portion of the coupling being provided via intermediate tissues. Other approaches may also be employed, for example, with one or more electrodes attached to the skin overlying the target nerve structures, implanted in cuffs around a target nerve, or the like. Regardless, the physician will typically seek to establish an appropriate treatment protocol by varying the electrical stimulation that is applied to the electrodes.
Current stimulation electrode placement/implantation techniques and known treatment setting techniques suffer from significant disadvantages. The nerve tissue structures of different patients can be quite different, with the locations and branching of nerves that perform specific functions and/or enervate specific organs being challenging to accurately predict or identify. The electrical properties of the tissue structures surrounding a target nerve structure may also be quite different among different patients, and the neural response to stimulation may be markedly dissimilar, with an electrical stimulation pulse pattern, frequency, and/or voltage that is effective to affect a body function for one patent potentially may impose significant pain on, or have limited effect for, another patient. Even in patients where implantation of a neurostimulation system provides effective treatment, frequent adjustments and changes to the stimulation protocol are often required before a suitable treatment program can be determined, often involving repeated office visits and significant discomfort for the patient before efficacy is achieved. While a number of complex and sophisticated lead structures and stimulation setting protocols have been implemented to seek to overcome these challenges, the variability in lead placement results, the clinician time to establish suitable stimulation signals, and the discomfort (and in cases the significant pain) that is imposed on the patient remain less than ideal. In addition, the lifetime and battery life of such devices is relatively short, such that implanted systems are routinely replaced every few years, which requires additional surgeries, patient discomfort, and significant costs to healthcare systems.
Furthermore, not all adjustments to neural stimulation systems have been implemented by clinicians. Patient devices can adjust stimulation or to turn off the neurostimulation system. Unfortunately, the wide variety of adjustments that can be made have the potential to confuse patients and/or eventually result in a significant reduction in long-term efficacy of these systems.
The tremendous benefits of these neural stimulation therapies have not yet been realized. Therefore, it is desirable to provide improved neurostimulation methods, systems and devices, as well as methods for implanting and configuring such neurostimulation systems for a particular patient or condition being treated. It would be particularly helpful to provide such systems and methods so as to improve ease of use by the physician in implanting and configuring the system, as well as to improve patient comfort and alleviation of symptoms for the patient. It would also be helpful to provide systems and methods to allow the patient to adjust the stimulation level delivered by such neurostimulation systems, where such adjustment is simple, unambiguous, and sufficiently limited to ensure the stimulation can remain within a clinically effective range.
A patient remote is provided to allow a patient to adjust the stimulation level of a neurostimulation system, which can include an electrical pulse generator coupled to an implanted electrical lead. The degree of adjustment permitted to the patient through the patient remote can be limited, such that while the patient can incrementally increase or decrease the therapy delivered by the neurostimulation system, so that the level of stimulation therapy by the neurostimulation system is maintained within a clinically effective range. By providing a controlled and limited range of adjustment to a patient through the patient remote, the patient is given a straightforward and simple tool for operation of the neurostimulation system, without presenting a selection of therapy or operational programs that may unnecessarily confuse a patient or take the neurostimulation system outside of the clinically effective range. The clinically effective range of the neurostimulation system can be determined by a physician or the clinician programmer when setting the parameters of the neurostimulation system. The patient remote can also allow a patient to turn off the neurostimulation system, which may be desirable for the patient when performing activities that may inadvertently interfere with, or be inadvertently interfered by, the neurostimulation system and the nerves stimulated by the neurostimulation system.
In some embodiments a patient remote according to the present disclosure is configured to wirelessly control a nerve-stimulating pulse generator coupled to an implantable lead in a patient, where the patient remote includes: a portable housing configured to be operable in a single hand of an operator. Circuitry may be at least partially disposed within the portable housing, and an activation switch can be on an exterior surface of the portable housing and coupled with the circuitry to reconfigure or transition the patient remote between an awake mode and an asleep mode. A stimulation-increase switch can be disposed on the exterior surface of the portable housing and coupled to the circuitry so as to wirelessly increase a stimulation level of the pulse generator when the patient remote is in the awake mode. Actuation of the stimulation-increase switch for a first period of time may increase the stimulation level (including by turn stimulation on stimulation if the pulse generator was previously off). Actuation of the stimulation-increase switch for a second period of time may restore the stimulation level of the pulse generator to a previously stored or last stored stimulation level (and may also turn stimulation on). The first period of time and the second period of time can be demarked by a threshold time. In some aspects, actuation of the stimulation-increase switch for the second period of time ramps the stimulation level to the previously stored or last stored stimulation level. As described in any of the embodiments herein, previously stored stimulation level can refer to a last stored stimulation level.
In other aspects, the patient remote can further include a stimulation-decrease switch disposed on the exterior surface of the portable housing configured to wirelessly decrease the stimulation level of the pulse generator, where when the activation switch of the patient remote is in the awake mode, actuation of the stimulation-decrease switch for the first period of time decreases the stimulation level or turns off stimulation of the pulse generator, and where actuation of the stimulation-decrease switch for the second period of time stores the stimulation level in a memory element and turns off the stimulation by the pulse generator. In further aspects, actuation of the stimulation-increase switch incrementally increases the stimulation level up to three or four stimulation levels above a baseline or nominal stimulation level and actuation of the stimulation-decrease switch incrementally decreases the stimulation level down respectively to three or two stimulation levels below the baseline stimulation level. As described herein, a baseline or nominal stimulation level can be the optimum stimulation level, which can be determined by the CP or can be set by the clinician. In some aspects, this nominal stimulation level can be determined based on sensory or motor responses, qualitative sensory feedback or various combinations thereof. In some embodiments, determination of the nominal stimulation level can be based in part on a threshold level of the selected electrodes and a maximum stimulation level based on patient comfort. In some embodiments, the nominal stimulation can be determined so that incremental adjustment of stimulation levels by the patient in either direction remains within a clinically effective range. In some aspects, each stimulation level increase or stimulation level decrease of the pulse generator comprises more than five percent (5%), optionally at least ten percent (10%) of a nominal stimulation level or a current stimulation level.
In many embodiments, the patient remote can further include a stimulation-level display disposed on the exterior surface of the portable housing. The patient remote may be configured to wirelessly communicate with the pulse generator and the stimulation-level display may be configured to indicate a current stimulation level of the pulse generator when the activation switch of the patient remote is switched from the asleep mode to the awake mode. In some aspects, the stimulation-level display can include a plurality of light emitting diodes, where a number of illuminated light emitting diodes indicates the current stimulation level of the pulse generator. In other aspects, the stimulation-level display can include at least seven light emitting diodes of at least two, three or four sizes, where a baseline stimulation level can be indicated by illumination of (for example) the first three or four light emitting diodes.
In further aspects, the patient remote can also include a therapy-remaining display disposed on the exterior surface of the portable housing, and can be configured to indicate therapy remaining status based on at least a charge or voltage remaining in a battery of the pulse generator and stimulation use parameters by the patient. In such aspects, the therapy-remaining display can include a light emitting diode having at least two contrasting colors or a single color with flashing and non-flashing modes or both to indicate if the pulse generator needs re-charging, is charging, or has sufficient charge for at least four days of nominal stimulation. In particular aspects, the therapy-remaining display light emitting diode can illuminate with a non-flashing green color to indicate at least four (4) days of therapy remaining, can illuminate with a non-flashing amber color to indicate two to four (2-4) days of therapy remaining, and can illuminate with a flashing amber color to indicate less than two (2) days of therapy remaining. In some aspects, the patient remote can further include an automatic fault condition indicator disposed on the exterior surface of the portable housing that is configured to provide an alert if the pulse generator is in a fault condition. In other aspects, the patient remote can further include a haptic indicator coupled to the portable housing that is configured to vibrate when a command from the patient remote has been executed by the pulse generator. In further aspects, the nerve-stimulating pulse generator can include an external or implantable pulse generator, and the implantable lead comprises at least one electrode configured for insertion into a foramen of a sacrum near a sacral nerve.
In other embodiments, a patient remote is configured to wirelessly control a nerve-stimulating pulse generator coupled to an implantable lead, the patient remote having: a portable housing configured to be operable in a single hand of an operator and circuitry at least partially disposed within the housing; an activation switch disposed within a recessed area of the portable housing so as to allow reconfiguration or transition between an awake mode and an asleep mode; a stimulation-increase switch disposed on an exterior surface of the portable housing, configured to wirelessly increase a stimulation level of the pulse generator; and a stimulation-decrease switch disposed on the exterior surface of the portable housing, configured to wirelessly decrease a stimulation level of the pulse generator; where when the recessed activation switch of the patient remote is in the asleep mode, the stimulation-increase switch and the stimulation-decrease switch are inactivated, and where when the recessed activation switch of the patient remote is in the awake mode, the patient remote is configured to wirelessly communicate with the pulse generator. In some aspects, the stimulation-increase switch and the stimulation-decrease switch are each disposed on a raised region of the exterior surface of the portable housing, where the stimulation-increase switch can further have a tactile feature that is larger in size than that of the stimulation-decrease switch. In other aspects, actuation of the stimulation-increase switch can incrementally increase the stimulation level up to three or four stimulation levels above a baseline stimulation level, and actuation of the stimulation-decrease switch can incrementally decrease the stimulation level down respectively to three or two stimulation levels below the baseline stimulation level. In further aspects, each stimulation level increase or stimulation level decrease of the pulse generator can be at least ten percent of a baseline stimulation level or a current stimulation level.
In some embodiments, the patient remote can further include a stimulation-level display disposed on the exterior surface of the portable housing, where the patient remote is configured to wirelessly communicate with the pulse generator and the stimulation-level display is configured to indicate a current stimulation level of the pulse generator, when the activation switch of the patient remote is switched from the asleep mode to the awake mode. In some aspects, the stimulation-level display can include a plurality of light emitting diodes, where a number of illuminated light emitting diodes indicates the current stimulation level of the pulse generator. In particular aspects, the stimulation-level display can include at least seven light emitting diodes of at least three or four sizes, where a baseline stimulation level can be indicated illumination of the first three or four light emitting diodes. In other aspects, the patient remote can further include a therapy-remaining display disposed on the exterior surface of the portable housing configured to indicate therapy remaining based on at least a charge of voltage remaining in a batter of the pulse generator a stimulation use parameters by the patient. In further aspects, the therapy-remaining display can include a light emitting diode having at least two contrasting colors or a single color with flashing and non-flashing modes to indicate if the pulse generator needs re-charging, is charging, or has sufficient charge for at least four days of nominal stimulation. In such aspects, the therapy-remaining display light emitting diode can illuminate with a non-flashing green color to indicate at least four (4) days of therapy remaining, can illuminate with a non-flashing amber color to indicate two to four (2-4) days of therapy remaining, and can illuminate with a flashing amber color to indicate less than two (2) days of therapy remaining. In some aspects, the patient remote can further have an automatic fault condition indicator disposed on the exterior surface of the portable housing configured to provide an alert if the pulse generator is in a fault condition. In other aspects, the patient remote can further have a haptic indicator coupled to the portable housing configured to vibrate when a command from the patient remote has been executed by the pulse generator.
In further embodiments, the present disclosure is directed to a method for controlling a nerve-stimulating pulse generator coupled to an implantable lead within a patient with a patient remote, the method including: wirelessly communicating with the pulse generator after an activation switch of the patient remote reconfigures or transitions the patient remote from an asleep mode to an awake mode; displaying a current stimulation setting of the pulse generator on a stimulation-level display of the patient remote; and wirelessly increasing a stimulation level or turning on stimulation of the pulse generator when a stimulation-increase switch of the patient remote is actuated for a first period of time or turning on and restoring stimulation of the pulse generator to a previously stored stimulation level when the stimulation-increase switch of the patient remote is actuated for a second period of time. In some aspects, the method can include wirelessly decreasing the stimulation level or turning off stimulation of the pulse generator when a stimulation-decrease switch of the patient remote is actuated for the first period of time or storing the stimulation level and turning off stimulation of the pulse generator when the stimulation-decrease switch of the patient remote is actuated for the second period of time. In other aspects, the method can further include automatically switching the patient remote from the awake mode to the asleep mode after a period of patient remote inactivity, wherein the period of inactivity comprises at least ten (10) seconds. In further aspects, the method can also include deactivating the stimulation-increase switch and stimulation-decrease switch of the patient remote when the activation switch of the patient remote is in the asleep mode. In yet further aspects, the method can include displaying a status of therapy remaining in the pulse generator on the patient remote, where the therapy remaining status is based on at least a charge or voltage remaining in a battery of the pulse generator and stimulation use parameters by the patient.
In some embodiments, the present disclosure is directed to a method for controlling a nerve-stimulating pulse generator coupled to an implantable lead within a patient with a patient remote, the method at least including actuating an activation switch to switch a patient remote between an awake mode and an asleep mode, where when the patient remote in the awake mode: actuating a stimulation-increase switch for a first period of time to turn on or incrementally increase the stimulation level of the pulse generator or actuating the stimulation-increase switch for a second period of time to turning on and restoring stimulation of the pulse generator to a previously stored stimulation level; and actuating a stimulation-decrease switch for the first period of time to turn off or incrementally decrease the stimulation level of the pulse generator or actuating the stimulation-decrease switch for the second period of time to store the current stimulation level and turn off stimulation of the pulse generator.
In other embodiments, the present disclosure is directed to an implantable nerve stimulation system having an implantable neurostimulator and a portable patient remote configured to wirelessly control the implantable neurostimulator, where the portable patient remote can include: an external housing having an oblong or rectangular shape; a stimulation-increase switch disposed on an exterior surface of the portable housing configured to wirelessly increase a stimulation level of the implantable neurostimulator; a stimulation-decrease switch disposed on the exterior surface of the portable housing configured to wirelessly decrease a stimulation level of the implantable neurostimulator; and a recessed activation switch disposed on the external housing and having an awake mode and an asleep mode, where when the recessed activation switch of the patient remote is in the asleep mode, the stimulation-increase switch and the stimulation-decrease switch are inactivated, and where when the recessed activation switch of the patient remote is in the awake mode, the patient remote is configured to wirelessly communicate with the implantable neurostimulator and actuation of the stimulation-increase switch for a first period of time increases the stimulation level or turns on stimulation of the implantable neurostimulator while actuation of the stimulation-increase switch for a second period of time turns on stimulation of the implantable neurostimulator and restores the stimulation level of the implantable neurostimulator to a previously stored stimulation level.
In further embodiments, the present disclosure is directed to a system for treating a patient with a disorder associated with a nerve, where the system includes a nerve-stimulating pulse generator having wireless communication circuitry and a plurality of stimulation levels; an implantable lead configured to be coupled with the pulse generator and implanted in the patient in operative communication with the nerve; and a patient remote. In such embodiments, the patent remote can include: a portable housing configured to be carried daily by the patient; circuitry disposed within the portable housing, the circuitry configured to wirelessly communicate with the wireless communication circuitry of the pulse generator; and a stimulation level varying switch disposed on the portable housing, the stimulation level switch coupled to the circuitry so as to wirelessly alter an applied stimulation level of the pulse generator when the switch is actuated, the applied stimulation level being selected from among the plurality of stimulation levels of the pulse generator so that actuation of the stimulation level switch allows the patient to select a level of stimulation being applied by the pulse generator to the lead; where the patient remote and pulse generator are configured so that the plurality of stimulation levels selectable by the patient using the patient remote define a monovariant range of stimulation levels extending from a least selectable stimulation level to a greatest selectable stimulation level.
Further areas of applicability of the present disclosure will become apparent from the detailed description provided hereinafter. It should be understood that the detailed description and specific examples, while indicating various embodiments, are intended for purposes of illustration only and are not intended to necessarily limit the scope of the disclosure.
The present invention relates to neurostimulation treatment systems and associated devices, as well as methods of treatment, implantation/placement and configuration of such treatment systems. In one particular embodiment, the invention relates to sacral nerve stimulation treatment systems configured to treat overactive bladder (“OAB”) and relieve symptoms of bladder related dysfunction. In addition, the descriptions herein may also be used to treat other forms of urinary dysfunction and to treat fecal dysfunction, therefore, throughout the description it should be understood that what is described for OAB applies equally to other forms of urinary dysfunction and fecal dysfunction. It will be appreciated however that the present invention may also be utilized for the treatment of pain or other indications, such as movement or affective disorders, as will be appreciated by one of skill in the art.
I. Neurostimulation Indications
Neurostimulation (or neuromodulation as may be used interchangeably hereunder) treatment systems, such as any of those described herein, can be used to treat a variety of ailments and associated symptoms, such as acute pain disorders, movement disorders, affective disorders, as well as bladder related dysfunction. Examples of pain disorders that may be treated by neurostimulation include failed back surgery syndrome, reflex sympathetic dystrophy or complex regional pain syndrome, causalgia, arachnoiditis, and peripheral neuropathy. Movement orders include muscle paralysis, tremor, dystonia and Parkinson's disease. Affective disorders include depressions, obsessive-compulsive disorder, cluster headache, Tourette syndrome and certain types of chronic pain. Bladder related dysfunctions include but are not limited to OAB, urge incontinence, urgency-frequency, and urinary retention. OAB can include urge incontinence and urgency-frequency alone or in combination. Urge incontinence is the involuntary loss or urine associated with a sudden, strong desire to void (urgency). Urgency-frequency is the frequent, often uncontrollable urges to urinate (urgency) that often result in voiding in very small amounts (frequency). Urinary retention is the inability to empty the bladder. Neurostimulation treatments can be configured to address a particular condition by effecting neurostimulation of targeted nerve tissues relating to the sensory and/or motor control associated with that condition or associated symptom.
In one aspect, the methods and systems described herein are particularly suited for treatment of urinary and fecal dysfunctions. These conditions have been historically under-recognized and significantly underserved by the medical community. OAB is one of the most common urinary dysfunctions. It is a complex condition characterized by the presence of bothersome urinary symptoms, including urgency, frequency, nocturia and urge incontinence. It is estimated that about 33 million Americans suffer from OAB. Of the adult population, about 30% of all men and 40% of all women live with OAB symptoms.
OAB symptoms can have a significant negative impact on the psychosocial functioning and the quality of life of patients. People with OAB often restrict activities and/or develop coping strategies. Furthermore, OAB imposes a significant financial burden on individuals, their families, and healthcare organizations. The prevalence of co-morbid conditions is also significantly higher for patients with OAB than in the general population. Co-morbidities may include falls and fractures, urinary tract infections, skin infections, vulvovaginitis, cardiovascular, and central nervous system pathologies. Chronic constipation, fecal incontinence, and overlapping chronic constipation occur more frequently in patients with OAB.
Conventional treatments of OAB generally include lifestyle modifications as a first course of action. Lifestyle modifications include eliminating bladder irritants (such as caffeine) from the diet, managing fluid intake, reducing weight, stopping smoking, and managing bowel regularity. Behavioral modifications include changing voiding habits (such as bladder training and delayed voiding), training pelvic floor muscles to improve strength and control of urethral sphincter, biofeedback and techniques for urge suppression. Medications are considered a second-line treatment for OAB. These include anti-cholinergic medications (oral, transdermal patch, and gel) and oral beta-3 adrenergic agonists. However, anti-cholinergics are frequently associated with bothersome, systemic side effects including dry mouth, constipation, urinary retention, blurred vision, somnolence, and confusion. Studies have found that more than 50% of patients stop using anti-cholinergic medications within 90 days due to a lack of benefit, adverse events, or cost.
When these approaches are unsuccessful, third-line treatment options suggested by the American Urological Association include intradetrusor (bladder smooth muscle) injections of Botulinum Toxin (BoNT-A), Percutaneous Tibial Nerve Stimulation (PTNS) and Sacral Nerve Stimulation (SNM). BoNT-A (Botox®) is administered via a series of intradetrusor injections under cystoscopic guidance, but repeat injections of Botox are generally required every 4 to 12 months to maintain effect and Botox may undesirably result in urinary retention. A number or randomized controlled studies have shown some efficacy of BoNT-A in OAB patients, but long-term safety and effectiveness of BoNT-A for OAB is largely unknown.
Alternative treatment methods, typically considered when the above approaches prove ineffective, is neurostimulation of nerves relating to the urinary system. Such neurostimulation methods include PTNS and SNM. PTNS therapy consists of weekly, 30-minute sessions over a period of 12 weeks, each session using electrical stimulation that is delivered from a hand-held stimulator to the sacral plexus via the tibial nerve. For patients who respond well and continue treatment, ongoing sessions, typically every 3-4 weeks, are needed to maintain symptom reduction. There is potential for declining efficacy if patients fail to adhere to the treatment schedule. Efficacy of PTNS has been demonstrated in a few randomized-controlled studies, however, long-term safety and effectiveness of PTNS is relatively unknown at this time.
II. Sacral Neuromodulation
SNM is an established therapy that provides a safe, effective, reversible, and long-lasting treatment option for the management of urge incontinence, urgency-frequency, and non-obstructive urinary retention. SNM therapy involves the use of mild electrical pulses to stimulate the sacral nerves located in the lower back. Electrodes are placed next to a sacral nerve, usually at the S3 level, by inserting the electrode leads into the corresponding foramen of the sacrum. The electrodes are inserted subcutaneously and are subsequently attached to an implantable pulse generator (IPG). The safety and effectiveness of SNM for the treatment of OAB, including durability at five years for both urge incontinence and urgency-frequency patients, is supported by multiple studies and is well-documented. SNM has also been approved to treat chronic fecal incontinence in patients who have failed or are not candidates for more conservative treatments.
Currently, SNM qualification has a trial phase, and is followed if successful by a permanent implant. The trial phase is a test stimulation period where the patient is allowed to evaluate whether the therapy is effective. Typically, there are two techniques that are utilized to perform the test stimulation. The first is an office-based procedure termed the Percutaneous Nerve Evaluation (PNE) and the other is a staged trial.
In the PNE, a foramen needle is typically used first to identify the optimal stimulation location, usually at the S3 level, and to evaluate the integrity of the sacral nerves. Motor and sensory responses are used to verify correct needle placement, as described in Table 1 below. A temporary stimulation lead (a unipolar electrode) is then placed near the sacral nerve under local anesthesia. This procedure can be performed in an office setting without fluoroscopy. The temporary lead is then connected to an external pulse generator (EPG) taped onto the skin of the patient during the trial phase. The stimulation level can be adjusted to provide an optimal comfort level for the particular patient. The patient will monitor his or her voiding for 3 to 7 days to see if there is any symptom improvement. The advantage of the PNE is that it is an incision free procedure that can be performed in the physician's office using local anesthesia. The disadvantage is that the temporary lead is not securely anchored in place and has the propensity to migrate away from the nerve with physical activity and thereby cause failure of the therapy. If a patient fails this trial test, the physician may still recommend the staged trial as described below. If the PNE trial is positive, the temporary trial lead is removed and a permanent quadri-polar tined lead is implanted along with an IPG under general anesthesia. Other neuromodulation applications may have any number of electrodes and more than one lead as the therapy may require.
A staged trial involves the implantation of the permanent quadri-polar tined stimulation lead into the patient from the start. It also requires the use of a foramen needle to identify the nerve and optimal stimulation location. The lead is implanted near the S3 sacral nerve and is connected to an EPG via a lead extension. This procedure is performed under fluoroscopic guidance in an operating room and under local or general anesthesia. The EPG is adjusted to provide an optimal comfort level for the patient and the patient monitors his or her voiding for up to two weeks. If the patient obtains meaningful symptom improvement, he or she is considered a suitable candidate for permanent implantation of the IPG under general anesthesia, typically in the upper buttock area, as shown in
In regard to measuring outcomes for SNM treatment of voiding dysfunction, the voiding dysfunction indications (e.g., urge incontinence, urgency-frequency, and non-obstructive urinary retention) are evaluated by unique primary voiding diary variables. The therapy outcomes are measured using these same variables. SNM therapy is considered successful if a minimum of 50% improvement occurs in any of primary voiding diary variables compared with the baseline. For urge incontinence patients, these voiding diary variables may include: number of leaking episodes per day, number of heavy leaking episodes per day, and number of pads used per day. For patients with urgency-frequency, primary voiding diary variables may include: number of voids per day, volume voided per void and degree of urgency experienced before each void. For patients with retention, primary voiding diary variables may include: catheterized volume per catheterization and number of catheterizations per day.
The mechanism of action of SNM is multifactorial and impacts the neuro-axis at several different levels. In patients with OAB, it is believed that pudendal afferents can activate the inhibitory reflexes that promote bladder storage by inhibiting the afferent limb of an abnormal voiding reflex. This blocks input to the pontine micturition center, thereby restricting involuntary detrusor contractions without interfering with normal voiding patterns. For patients with urinary retention, SNM is believed to activate the pudendal nerve afferents originating from the pelvic organs into the spinal cord. At the level of the spinal cord, pudendal afferents may turn on voiding reflexes by suppressing exaggerated guarding reflexes, thus relieving symptoms of patients with urinary retention so normal voiding can be facilitated. In patients with fecal incontinence, it is hypothesized that SNM stimulates pudendal afferent somatic fibers that inhibit colonic propulsive activity and activates the internal anal sphincter, which in turn improves the symptoms of fecal incontinence patients. The present invention relates to a system adapted to deliver neurostimulation to targeted nerve tissues in a manner that disrupt, inhibit, or prevent neural activity in the targeted nerve tissues so as to provide therapeutic effect in treatment of OAB or bladder related dysfunction. In one aspect, the system is adapted to provide therapeutic effect by neurostimulation without inducing motor control of the muscles associated with OAB or bladder related dysfunction by the delivered neurostimulation. In another aspect, the system is adapted to provide such therapeutic effect by delivery of sub-threshold neurostimulation below a threshold that induces paresthesia and/or neuromuscular response or to allow adjustment of neurostimulation to delivery therapy at sub-threshold levels.
While conventional approaches have shown efficacy in treatment of bladder related dysfunction, there exists a need to improve positioning of the neurostimulation leads and consistency between the trial and permanent implantation positions of the lead. Neurostimulation relies on consistently delivering therapeutic stimulation from a pulse generator, via one or more neurostimulation electrodes, to particular nerves or targeted regions. The neurostimulation electrodes are provided on a distal end of an implantable lead that can be advanced through a tunnel formed in patient tissue. Implantable neurostimulation systems provide patients with great freedom and mobility, but it may be easier to adjust the neurostimulation electrodes of such systems before they are surgically implanted. It is desirable for the physician to confirm that the patient has desired motor and/or sensory responses before implanting an IPG. For at least some treatments (including treatments of at least some forms of urinary and/or fecal dysfunction), demonstrating appropriate motor responses may be highly beneficial for accurate and objective lead placement while the sensory response may not be required or not available (e.g., patient is under general anesthesia).
Placement and calibration of the neurostimulation electrodes and implantable leads sufficiently close to specific nerves can be beneficial for the efficacy of treatment. Accordingly, aspects and embodiments of the present disclosure are directed to aiding and refining the accuracy and precision of neurostimulation electrode placement. Further, aspects and embodiments of the present disclosure are directed to aiding and refining protocols for setting therapeutic treatment signal parameters for a stimulation program implemented through implanted neurostimulation electrodes.
Prior to implantation of the permanent device, patients may undergo an initial testing phase to estimate potential response to treatment. As discussed above, PNE may be done under local anesthesia, using a test needle to identify the appropriate sacral nerve(s) according to a subjective sensory response by the patient. Other testing procedures can involve a two-stage surgical procedure, where a quadri-polar tined lead is implanted for a testing phase to determine if patients show a sufficient reduction in symptom frequency, and if appropriate, proceeding to the permanent surgical implantation of a neuromodulation device. For testing phases and permanent implantation, determining the location of lead placement can be dependent on subjective qualitative analysis by either or both of a patient or a physician.
In exemplary embodiments, determination of whether or not an implantable lead and neurostimulation electrode is located in a desired or correct location can be accomplished through use of electromyography (“EMG”), also known as surface electromyography. EMG, is a technique that uses an EMG system or module to evaluate and record electrical activity produced by muscles, producing a record called an electromyogram. EMG detects the electrical potential generated by muscle cells when those cells are electrically or neurologically activated. The signals can be analyzed to detect activation level or recruitment order. EMG can be performed through the skin surface of a patient, intramuscularly or through electrodes disposed within a patient near target muscles, or using a combination of external and internal structures. When a muscle or nerve is stimulated by an electrode, EMG can be used to determine if the related muscle is activated, (i.e. whether the muscle fully contracts, partially contracts, or does not contract) in response to the stimulus. Accordingly, the degree of activation of a muscle can indicate whether an implantable lead or neurostimulation electrode is located in the desired or correct location on a patient. Further, the degree of activation of a muscle can indicate whether a neurostimulation electrode is providing a stimulus of sufficient strength, amplitude, frequency, or duration to affect a treatment regimen on a patient. Thus, use of EMG provides an objective and quantitative means by which to standardize placement of implantable leads and neurostimulation electrodes, reducing the subjective assessment of patient sensory responses.
In some approaches, positional titration procedures may optionally be based in part on a paresthesia or pain-based subjective response from a patient. In contrast, EMG triggers a measureable and discrete muscular reaction. As the efficacy of treatment often relies on precise placement of the neurostimulation electrodes at target tissue locations and the consistent, repeatable delivery of neurostimulation therapy, using an objective EMG measurement can substantially improve the utility and success of SNM treatment. The measureable muscular reaction can be a partial or a complete muscular contraction, including a response below the triggering of an observable motor response, such as those shown in Table 1, depending on the stimulation of the target muscle. In addition, by utilizing a trial system that allows the neurostimulation lead to remain implanted for use in the permanently implanted system, the efficacy and outcome of the permanently implanted system is more consistent with the results of the trial period, which moreover leads to improved patient outcomes.
In one aspect, the clinician programmer 60 is used by a physician to adjust the settings of the EPG and/or IPG while the lead is implanted within the patient. The clinician programmer can be a tablet computer used by the clinician to program the IPG, or to control the EPG during the trial period. The clinician programmer can also include capability to record stimulation-induced electromyograms to facilitate lead placement and programming. The patient remote 70 can allow the patient to turn the stimulation on or off, or to vary stimulation from the IPG while implanted, or from the EPG during the trial phase.
In another aspect, the clinician programmer 60 has a control unit which can include a microprocessor and specialized computer-code instructions for implementing methods and systems for use by a physician in deploying the treatment system and setting up treatment parameters. The clinician programmer generally includes a user interface which can be a graphical user interface, an EMG module, electrical contacts such as an EMG input that can couple to an EMG output stimulation cable, an EMG stimulation signal generator, and a stimulation power source. The stimulation cable can further be configured to couple to any or all of an access device (e.g., a foramen needle), a treatment lead of the system, or the like. The EMG input may be configured to be coupled with one or more sensory patch electrode(s) for attachment to the skin of the patient adjacent a muscle (e.g., a muscle enervated by a target nerve). Other connectors of the clinician programmer may be configured for coupling with an electrical ground or ground patch, an electrical pulse generator (e.g., an EPG or an IPG), or the like. As noted above, the clinician programmer can include a module with hardware and computer-code to execute EMG analysis, where the module can be a component of the control unit microprocessor, a pre-processing unit coupled to or in-line with the stimulation and/or sensory cables, or the like.
In some aspects, the clinician programmer is configured to operate in combination with an EPG when placing leads in a patient body. The clinician programmer can be electronically coupled to the EPG during test simulation through a specialized cable set. The test simulation cable set can connect the clinician programmer device to the EPG and allow the clinician programmer to configure, modify, or otherwise program the electrodes on the leads connected to the EPG.
The electrical pulses generated by the EPG and IPG are delivered to one or more targeted nerves via one or more neurostimulation electrodes at or near a distal end of each of one or more leads. The leads can have a variety of shapes, can be a variety of sizes, and can be made from a variety of materials, which size, shape, and materials can be tailored to the specific treatment application. While in this embodiment, the lead is of a suitable size and length to extend from the IPG and through one of the foramen of the sacrum to a targeted sacral nerve, in various other applications, the leads may be, for example, implanted in a peripheral portion of the patient's body, such as in the arms or legs, and can be configured to deliver electrical pulses to the peripheral nerve such as may be used to relieve chronic pain. It is appreciated that the leads and/or the stimulation programs may vary according to the nerves being targeted.
Properties of the electrical pulses can be controlled via a controller of the implanted pulse generator. In some embodiments, these properties can include, for example, the frequency, strength, pattern, duration, or other aspects of the electrical pulses. These properties can include, for example, a voltage, a current, or the like. This control of the electrical pulses can include the creation of one or more electrical pulse programs, plans, or patterns, and in some embodiments, this can include the selection of one or more pre-existing electrical pulse programs, plans, or patterns. In the embodiment depicted in
In some embodiments, the trial neurostimulation system utilizes an EPG 80 within an EPG patch 81 that is adhered to the skin of a patient and is coupled to the implanted neurostimulation lead 20 through a lead extension 22, which is coupled with the lead 20 through a connector 21. This extension and connector structure allows the lead to be extended so that the EPG patch can be placed on the abdomen and allows use of a lead having a length suitable for permanent implantation should the trial prove successful. This approach may utilize two percutaneous incisions, the connector provided in the first incision and the lead extensions extending through the second percutaneous incision, there being a short tunneling distance (e.g., about 10 cm) there between. This technique may also minimize movement of an implanted lead during conversion of the trial system to a permanently implanted system.
In one aspect, the EPG unit is wirelessly controlled by a patient remote and/or the clinician programmer in a similar or identical manner as the IPG of a permanently implanted system. The physician or patient may alter treatment provided by the EPG through use of such portable remotes or programmers and the treatments delivered are recorded on a memory of the programmer for use in determining a treatment suitable for use in a permanently implanted system. The clinician programmer can be used in lead placement, programming and/or stimulation control in each of the trial and permanent nerve stimulation systems. In addition, each nerve stimulation system allows the patient to control stimulation or monitor battery status with the patient remote. This configuration is advantageous as it allows for an almost seamless transition between the trial system and the permanent system. From the patient's viewpoint, the systems will operate in the same manner and be controlled in the same manner, such that the patient's subjective experience in using the trial system more closely matches what would be experienced in using the permanently implanted system. Thus, this configuration reduces any uncertainties the patient may have as to how the system will operate and be controlled such that the patient will be more likely to convert a trial system to a permanent system.
As shown in the detailed view of
In one aspect, the IPG is rechargeable wirelessly through conductive coupling by use of a charging device 50 (CD), which is a portable device powered by a rechargeable battery to allow patient mobility while charging. The CD is used for transcutaneous charging of the IPG through RF induction. The CD can either be either patched to the patient's skin using an adhesive or can be held in place using a belt 53 or by an adhesive patch 52, such as shown in the schematic of
The system may further include a patient remote 70 and clinician programmer 60, each configured to wirelessly communicate with the implanted IPG, or with the EPG during a trial, as shown in the schematic of the nerve stimulation system in
One or more properties of the electrical pulses can be controlled via a controller of the IPG or EPG. In some embodiments, these properties can include, for example, the frequency, strength, pattern, duration, or other aspects of the timing and magnitude of the electrical pulses. These properties can further include, for example, a voltage, a current, or the like. This control of the electrical pulses can include the creation of one or more electrical pulse programs, plans, or patterns, and in some embodiments, this can include the selection of one or more pre-existing electrical pulse programs, plans, or patterns. In one aspect, the IPG 10 includes a controller having one or more pulse programs, plans, or patterns that may be created and/or pre-programmed. In some embodiments, the IPG can be programmed to vary stimulation parameters including pulse amplitude in a range from 0 mA to 10 mA, pulse width in a range from 50 μs to 500 μs, pulse frequency in a range from 5 Hz to 250 Hz, stimulation modes (e.g., continuous or cycling), and electrode configuration (e.g., anode, cathode, or off), to achieve the optimal therapeutic outcome specific to the patient. In particular, this allows for an optimal setting to be determined for each patient even though each parameter may vary from person to person.
As shown in
In some embodiment, such as that shown in
In one aspect, utilization of ceramic material provides an efficient, radio-frequency-transparent window for wireless communication with the external patient remote and clinician's programmer as the communication antenna is housed inside the hermetic ceramic case. This ceramic window has further facilitated miniaturization of the implant while maintaining an efficient, radio-frequency-transparent window for long term and reliable wireless communication between the IPG and external controllers, such as the patient remote and clinician programmer. The IPG's wireless communication is generally stable over the lifetime of the device, unlike prior art products where the communication antenna is placed in the header outside the hermetic case. The communication reliability of such prior art devices tends to degrade due to the change in dielectric constant of the header material in the human body over time.
In another aspect, the ferrite core is part of the charging coil assembly 15, shown in
In order to confirm correct lead placement, it is desirable for the physician to confirm that the patient has both adequate motor and sensory responses before transitioning the patient into the staged trial phase or implanting the permanent IPG. However, sensory response is a subjective evaluation and may not always be available, such as when the patient is under general anesthesia. Experiments have shown that demonstrating appropriate motor responses is advantageous for accurate placement, even if sensory responses are available. As discussed above, EMG is a tool which records electrical activity of skeletal muscles. This sensing feature provides an objective criterion for the clinician to determine if the sacral nerve stimulation results in adequate motor response rather than relying solely on subjective sensory criteria. EMG can be used not only to verify optimal lead position during lead placement, but also to provide a standardized and more accurate approach to determine electrode thresholds, which in turn provides quantitative information supporting electrode selection for programming. Using EMG to verify activation of motor responses can further improve the lead placement performance of less experienced operators and allow such physicians to perform lead placement with confidence and greater accuracy.
In one aspect, the system is configured to have EMG sensing capability during re-programming, which can be particularly valuable. Stimulation levels during re-programming are typically low to avoid patient discomfort which often results in difficult generation of motor responses. Involuntary muscle movement while the patient is awake may also cause noise that is difficult for the physician to differentiate. In contrast to conventional approaches, EMG allows the clinician to detect motor responses at very low stimulation levels (e.g., sub-threshold), and help them distinguish a motor response originated by sacral nerve stimulation from involuntary muscle movement.
Referring to
In some embodiments, the IPG, as well as the EPG, may be configured with two stimulation modes: continuous mode and cycling mode, such as shown in
In some embodiments, the IPG/EPG is configured with a ramping feature, such as shown in the example of
The patient remote (e.g.
The degree of adjustment permitted to the patient through the patient remote can be limited, such that while the patient can incrementally increase or decrease the therapy delivered by the pulse generator, and can turn stimulation on or off, the level of stimulation therapy by the pulse generator whenever the pulse generator is applying stimulation is maintained within a clinically effective combination of settings. By providing a limited range of adjustment to a patient through the patient remote, the patient is given a straightforward and simple tool for situational control of the pulse generator and overall neurostimulation system, allowing for the use of different stimulation levels (including no stimulation when appropriate) while the patient is awake, while the patient is asleep, while the patient is engaged in specific activities, or in other situations. However, the patient may not be presented with a selection of alternative therapies or multivariate operational programs via the patient remote that may confuse the patient or take the pulse generator outside of a clinically effective range. In some aspects, the patient remote can be configured to provide monovariant control to the patient. For example, the patient remote can be limited to varying a stimulation level of the stimulation program, while the other attributes of the stimulation program (e.g. duration, electrode configuration, pulse width, etc.) are maintained. The clinically effective range of the pulse generator can be determined by a physician or the clinician programmer when setting the parameters of the pulse generator and neurostimulation system.
The patient remote can allow a patient to turn on and turn off the pulse generator, where turning off the pulse generator may be desirable for the patient when performing activities that may inadvertently interfere with, or be inadvertently interfered by, an active pulse generator and the nerves stimulated by the pulse generator. For example, as noted in Table 1 above, innervation of the S3 sacral nerve can cause a response in the plantar flexion of the great toe or other toes. Thus, it may be desirable to provide a patient the option to turn off the pulse generator while driving, carrying heavy objects, or performing other activities that can strain the foot or toes and may thereby inadvertently trigger a pulling sensation in the rectum. Moreover, it may be desirable to provide a patient the option to automatically restore the pulse generator to a previous level of stimulation when the pulse generator is turned on after a period of being turned off. In many cases, the previous level of stimulation can be the last stored stimulation level of the patient remote. In further implementations, the patient remote can provide the patient with an indication of battery status and/or therapy remaining for the neurostimulation system and pulse generator.
Structurally, the patient remote can include a portable housing, with one or more switches and one or more displays on or embedded within the exterior surface of the portable housing. The patient remote can have an activation switch and a stimulation-increase switch disposed on an exterior surface of the patient remote, allowing the patient (or other operator) to activate the patient remote and then to instruct the neurostimulation system to increase the stimulation level of the pulse generator. The patent remote can also include any combination of a stimulation-decrease switch (allowing the patient to decrease the stimulation level), a stimulation-level display, a therapy-remaining display, and/or a fault condition display disposed on the exterior surface of the patient remote.
In other words, the portable housing of the patient remote can be sized or dimensioned so as to fit within a single hand of a patient. The patient remote can accordingly be operable within a single hand of a patient, or another operator. Further, in the context of the present disclosure, the switches of the patient remote can instead be buttons, formed as part of the body of the patient remote, or formed to pass through shaped holes in the surface of the patient remote. In implementations of the patient remote having buttons, the buttons can be spring biased or otherwise supported so as to provide a degree of resistance to actuation and/or to restore a button to a default status after actuation is completed and the button is released. Any given switch or button on the patient remote can be located within a depression of the external surface of the patient remote, on a flat surface of the external surface of the patient remote, or on a convex surface of the external surface of the patient remote. Moreover, any given switch or button on the patient remote can have a profile that is flush with the external surface of the patient remote, elevated from the external surface of the patient remote, or inset/depressed within the external surface of the patient remote.
While the terms “switches” and “buttons” are used in the described embodiments to illustrate various concepts, it is appreciated that such terms can encompass any actuation feature that is operable by a user to effect a change in state associated with the patient remote. A change in state can include a change in an activation state of the patient remote, or a mode of the pulse generator and a stimulation level of the IPG or EPG that is controlled by the patient remote. For example, the actuation feature can be a button, lever, knob, or an optical or touch sensor or any suitable feature that allows a user to effect the change in state by interaction with the feature. In some embodiments, the actuation features can include portions of a touch screen displayed to a user.
The patient remote 900 can include within the interior of the portable housing 902 transmission circuitry configured to interface with the pulse generator, a battery that functions as a power source for the patient remote, and control electronics. Control electronics in the interior of the portable housing 902 can be operatively coupled to relay signals to the transmission circuitry for controlling control the pulse generator corresponding to actuation of the one or more switches disposed on the exterior surface of the portable housing 902. In alternative aspects, the patient remote 900 can include circuitry to communicate with the clinician programmer (CP).
The transmission circuitry can include a radio frequency (RF) transmitter that communicates with other system elements on the Medical Implant Communication Service (MICS) frequency band (MedRadio 402-405 MHz). The wireless communication between the patient remote 900 and the pulse generator to which the patient remote 900 sends instructions can have an operational range of up to three feet, in addition to transmission through the tissue of a patient, in embodiments where the pulse generator is an IPG implanted in the patient. A patient remote 900 having any or all of an activation switch 904, stimulation-increase switch 906, or stimulation-decrease switch 908 (where any or all of activation switch 904, stimulation-increase switch 906, or stimulation-decrease switch 908 can be buttons) disposed on the exterior surface of the portable housing 902 can be configured such that actuation of such switches and/or buttons (where actuation can be depressing, triggering, toggling, or otherwise operating the switch or button) causes the control electronics and/or transmission circuitry of the patient remote 900 to relay a signal to a neurostimulation system and/or to execute a function of the patient remote 900 itself. In some aspects, the battery that powers the patient remote 900 can be a permanent battery having an operational life of three or more years. In alternative aspects, the battery that powers the patient remote 900 can be a replaceable or a rechargeable battery.
In some embodiments, the activation switch 904 (alternatively referred to as a “link switch”) can be disposed on the control surface 903, and in particular embodiments the activation switch 904 can be disposed in a recessed region of the control surface 903. In embodiments where the activation switch 904 is disposed in a recess of the control surface 903, activation switch 904 is designed to be actuation due to deliberate effort. In other words, where the structure of the activation switch 904 is disposed within the recess, accidental or inadvertent actuation of the activation switch 904 due to incidental physical contact with the exterior surface of the portable housing 902 or contact with other sections of the control surface 903 can be avoided by providing sufficient physical resistance to a throw of the switch. More succinctly, in various embodiments, the activation switch 904 is recessed so as to avoid accidental depression by the user when the patient remote 900 is stored in a pocket or purse of the patient. In these embodiments, the recess can have a sufficient depth relative to the size of the activation switch 904 such that the height of the activation switch 904 is shorter than the depth of the recess, and thus the activation switch 904 does not extend out of the recess.
The activation switch 904 operates to switch the patient remote 900 between an asleep mode and an awake mode. When the patient remote 900 is in an asleep mode, actuation of the activation switch 904 causes the patient remote to switch to the awake mode and to interrogate the neurostimulator to wirelessly retrieve data regarding the status of the neurostimulation system and/or pulse generator. The data retrieved from the neurostimulation system can include the current stimulation level of the pulse generator, which can be stored in a processor and/or memory of the pulse generator. When the patient remote 900 is in the awake mode, actuation of the activation switch 904 causes the patient remote 900 to switch to the asleep mode. When the patient remote 900 is in the asleep mode, the stimulation-increase switch 906 and the stimulation-decrease switch 908 (both also disposed on the control surface 903) are inactivated, such that actuation of either the stimulation-increase switch 906 or the stimulation-decrease switch 908 does not cause the patient remote 900 to send any signal with transmission circuitry within the portable housing 902. When the patient remote 900 is in the awake mode, the stimulation-increase switch 906 and the stimulation-decrease switch 908 are active, such that actuation of either the stimulation-increase switch 906 or the stimulation-decrease switch 908 causes the patient remote 900 to send a corresponding instruction signal with transmission circuitry within the portable housing 902. When in the awake mode, if the patient remote 900 is inactive for a set period of time (e.g. none of the activation switch 904, stimulation-increase switch 906, or stimulation-decrease switch 908 are actuated for the set period of time), the patient remote can automatically switch to the asleep mode. In some aspects, the set period of time after which the patient remote 900 will automatically switch to the asleep mode can be five (5) to sixty (60) seconds, or any increment or gradient of time within that range. In specific aspects, the set period of time after which the patient remote 900 will automatically switch to the asleep mode can be ten (10) seconds.
The control surface 903 can include a stimulation-increase switch 906 coupled to control electronics and transmission circuitry disposed within the portable housing 902. Actuation of the stimulation-increase switch 906 can relay an instruction signal to the pulse generator (i.e., through the control electronics and transmission circuitry of the patient remote 900), where the instruction signal can be selected based on duration of time that the stimulation-increase switch 906 is actuated. When the stimulation-increase switch 906 is actuated for a first period of time, the patient remote 902 can send an instruction signal to the pulse generator to incrementally increase the stimulation level of the pulse generator. The first period of time will generally be a period of time that is shorter than a threshold. The threshold may generally be between 0.25 and 5 seconds, with the time period for a longer switch actuation threshold time being sufficient to assure that the longer duration switch actuation is clearly intentional, typically being three seconds or more. Increasing the stimulation level of the pulse generator can be limited to a maximum selectable level of therapy. When the stimulation-increase switch 906 is actuated for a second, longer period of time, the patient remote 902 can send an instruction signal to the pulse generator to restore the stimulation level of the pulse generator to a previously stored stimulation level. The second period of time can be three seconds or more. In some aspects, when the pulse generator is instructed to restore the previously stored stimulation level, the pulse generator can gradually ramp up (as shown in
In situations where a patient has turned off the pulse generator, providing a method to automatically return the stimulation of the pulse generator to a previously stored stimulation level allows a patient to efficiently and automatically restore the neurostimulation system to a desired function or status, avoiding the need for repetitive adjustment of the stimulation level. In many embodiments, the previously stored stimulation level can be the last stimulation level the pulse generator was set to before turning off the neurostimulation system. In some aspects, the data indicating the last stimulation level can be stored in a memory of the pulse generator which is retrieved by the patent remote 900 when the patient remote 900 switches from the asleep mode to the awake mode. In other aspects, the stimulation level can be stored in a memory of the circuitry within the patient remote 900 portable housing 902.
The stimulation-increase switch 906 can further have a visible and/or tactile surface or feature shaped to indicate to an operator that the stimulation-increase switch 906 is configured to increase or restore the stimulation level of the pulse generator (e.g., as an upward arrow, as a plus sign, etc.). In some aspects, the stimulation-increase switch 906 can be relatively larger than any stimulation-decrease switch 908 also disposed on the exterior of the portable housing 902.
The control surface 903 can also include a stimulation-decrease switch 908 coupled to control electronics and transmission circuitry disposed within the portable housing 902. Actuation of the stimulation-decrease switch 908 can relay an instruction signal to the pulse generator, where the instruction signal can be selected based on duration of time that the stimulation-decrease switch 908 is actuated. When the stimulation-decrease switch 908 is actuated for the first period of time, the patient remote 902 can send a signal to the pulse generator incrementally decrease the stimulation level of the pulse generator, with the time period for a longer switch actuation threshold time being sufficient to assure that the longer duration switch actuation is clearly intentional, typically being three seconds or more. If the stimulation level of the pulse generator is at the minimum selectable level of therapy, actuation of the stimulation-decrease switch 908 for the first period of time can turn off stimulation by the pulse generator. When the stimulation-decrease switch 908 is actuated for a second period of time, the patient remote 902 can send a signal to the pulse generator to store the status of the current stimulation level in a memory and turn off stimulation by the pulse generator. The second period of time can be three seconds or more. In some aspects, when the pulse generator is instructed to turn off stimulation, the pulse generator can gradually ramp down (as shown in
The stimulation-decrease switch 908 can further have a visible and/or tactile surface or feature shaped to indicate to an operator that the stimulation-decrease switch 908 is configured to decrease the stimulation level of the pulse generator or turn off stimulation by the pulse generator (e.g., as a downward arrow, as a minus sign, etc.). In some aspects, the memory in which the stimulation level is stored in the patient remote, or alternately the memory may be stored in the pulse generator. In alternative aspects, the stimulation-increase switch 906 and the stimulation-decrease switch 908 can be relatively equal in size.
The incremental increase or decrease of pulse generator stimulation level by the patient remote 900 can be proportional to an existing or current stimulation level. In many aspects, the incremental increase or decrease of pulse generator stimulation level can be a change of a predetermined degree. The predetermined degree can be a percentage of a stimulation level, a fraction of a stimulation level, a specific or static increment of stimulation level, a proportional increment of stimulation level, a range-dependent increment of stimulation level, a variable increment of stimulation level, or the like. In some embodiments, each incremental change can be five percent (5%), more than five percent (5%), or ten percent (10%) of the existing stimulation level, a maximum stimulation level, or a baseline stimulation level. For example, if a pulse generator is delivering treatment at a stimulation level of 2.0 mA, a single step up increasing the stimulation level can be 0.2 mA (10% of 2.0 mA), thereby increasing stimulation to 2.2 mA. A subsequent step up increasing the stimulation level can be 0.22 mA (10% of 2.2 mA), thereby increasing stimulation to 2.42 mA. Similarly, if a pulse generator is delivering treatment at a stimulation level of 4.0 mA, a single step down decreasing the stimulation level can be 0.4 mA (10% of 4.0 mA), thereby decreasing stimulation to 3.6 mA. In various embodiments, the step size by which the pulse generator stimulation level is changed can be 1% to 25% of the existing stimulation level, or any increment or gradient of a percentage within that range. The number of available treatment levels may be between 3 and 15, typically being between 4 and 10, and often being between 5 and 8.
In some alternative embodiments, for example, if a pulse generator is delivering treatment at a baseline or nominal stimulation level of 3.0 mA, a single step up increasing the stimulation level can be ten percent of the baseline stimulation, 0.3 mA (10% of 3.0 mA), thereby increasing stimulation to 3.3 mA. A subsequent step up increasing the stimulation level can also be based on the baseline stimulation level, that step again being 0.3 mA, thereby increasing stimulation to 3.6 mA. Further within this exemplary embodiment, a single step down decreasing stimulation from a baseline level of 3.0 mA can lower the current stimulation level to 2.7 mA, and a subsequent step down can decrease the current stimulation level to 2.4 mA.
In further alternative embodiments, each step of stimulation level can be based on a percentage of a maximum stimulation level. For example, if a pulse generator has a maximum treatment stimulation level of 4.0 mA, each step of stimulation level change can be ten percent of the maximum stimulation level, 0.4 mA (10% of 4.0 mA). Thus, relative to the maximum stimulation level, a single step down decreasing the stimulation level can be at 3.6 mA, a subsequent step down decreasing the stimulation level can be at 3.2 mA, and so forth.
In other alternative embodiments, the patient remote 900 can operate having an automated proportional stimulation step level increments. For example, when the available stimulation range is within a lower amplitude range, the incremental steps can be smaller than those associated with a higher amplitude range. For example, under conditions where the amplitude range of stimulation level for the patient remote 900 is less than 1.0 milliamp (<1.0 mA), the default increment for a step of simulation level can be 0.05 mA. However, under conditions where the amplitude range of stimulation level for the patient remote 900 is from 1.0 to 3.0 milliamps (1.0-3.0 mA), the default increment for a step of simulation level can be 0.10 mA. Further, under conditions where the amplitude range of stimulation level for the patient remote 900 is greater than 3.0 milliamps (>3.0 mA), the default increment for a step of simulation level can be 0.20 mA. The proportional change in stimulation level step can be varied depending on the amount of treatment required, the number of amplitude ranges, the breadth of amplitude ranges, and/or according to other factors controlling the operation of the patient remote 900. The above described incremental steps can also be applied when determining electrode thresholds during electrode characterization and/or programming.
In some embodiments, the patient remote 900 can be set to incrementally adjust stimulation by a step-size defined by a relationship between a maximum stimulation level (Imax) and a baseline, also referred to as a nominal or normal stimulation level (In). For example, the Imax and the In can be determined and set-up by a physician programming the patient remote 900 via the clinician programmer. The amplitude of Imax can be set according to the comfort level of a patient (e.g. stimulation level just below where any pain or discomfort is reported by the patient). Where a difference between Imax and In is ΔI, the increment step size can be a set proportion or percentage of ΔI, for example steps sizes of ½ ΔI, ⅓ ΔI, or ¼ ΔI. In some embodiments, the CP automatically sets such an incremental step size (e.g. ⅓ ΔI) with the IPG or EPG, for example during electrode characterization and/or programming. Likewise, patient remote 900 can be programmed with a step-size that corresponds to the step-size used by the CP in programming the IPG or EPG. The amount by which the stimulation levels can be adjusted below the nominal stimulation level (e.g. lower range) can be defined to mirror the incremental range between Imax and In (e.g. upper range). For example, where the increment step size is defined as ⅓ ΔI, the range over which the stimulation level can be incrementally adjusted by the patient remote includes seven stimulation levels, where the nominal or normal stimulation level In is in the middle of those seven stimulation levels, incrementing up or down at ⅓ ΔI per step allows for a range of stimulation levels that reaches the maximum stimulation level Imax on one end of the available treatment range, and a minimum stimulation level that mirrors Imax on the other end of the available treatment range, as shown below:
(where +ΔI above In is Imax and −ΔI is Imin).
By programming the patient remote 900 to increment stimulation of a coupled pulse generator by a predetermined degree such as ⅓ΔI, a full range of stimulation levels can be achieved relative to a relationship between Imax that matches the comfort level of a patient and the nominal stimulation level corresponding to optimized clinically effective therapy. It is understood that the selection of a stimulation level increment step size by programming the patient remote can allow for setting of a stimulation level increment step to be a specific percentage of a maximum stimulation level, or proportional to a range between the maximum stimulation level and the nominal stimulation level. In some embodiments, the pulse generator is configured to adjust stimulation incrementally according to a step-size, such as described in any of the embodiments described herein, in response to an increase or decrease command received from the patient remote. In one aspect, the command can include the step-size by which the stimulation level is adjusted or the command can invoke an incremental adjustment based on a step-size increment stored on a memory of the pulse generator.
In various embodiments, the patient remote 900 can increase and/or decrease the stimulation level by a predetermined percentage. In some embodiments, the predetermined percentage is a set percentage within a range between 5% and 20%, such as about 10% (+/−2%). In some embodiments, the predetermined percentage is the same for incremental increases and decreases, while in other embodiments, the increase increment differs from that of the decrease increment.
The control surface 903 can include a stimulation-level display 910 embedded in the portable housing 902, and electronically coupled to control electronics and transmission circuitry disposed within the portable housing 902 such that the stimulation-level display 910 can indicate the stimulation level being delivered by the pulse generator to a patient. In some embodiments, the stimulation-level display 910 can include a plurality of lights or light emitting diodes (LEDs) arranged on the control surface, where an illuminated subset of the total number of the plurality of lights or LEDs can indicate the current stimulation level of the pulse generator. In some aspects, the stimulation-level display 910 can include seven (7) white-light LEDs. The stimulation-level display 910 can have the plurality of LEDs arranged in a pattern to reflect increases and decreases to the stimulation level of the pulse generator. In arrangements of the stimulation-level display 910 with seven LEDs as illustrated in
As noted above, a patient remote 900 can be configured to be used with any appropriate respective pulse generator, such that the patient remote 900 can link with and wirelessly communicate with only a single EPG or IPG, so as to avoid inadvertent and unintentional activation, alteration, or triggering of stimulation of other pulse generators. Accordingly, in implementations of the system, a specific patient remote 900 can be paired with a specific pulse generator (e.g., an IPG, an EPG, or the like) such that the patient remote 900 will only, or at least primarily, operate to interact with the paired pulse generator. The pairing of a patient remote 900 and a specific pulse generator can be established by setting the patient remote 900 and the specific pulse generator to transmit and receive data at the same predetermined wireless or radio frequency. While the clinician programmer can be used to set up or configure a patient remote 900, or establish the paring between a patient remote 900 and a pulse generator, in operation for managing stimulation levels, the patient remote 900 only and/or directly communicates with the pulse generator.
The available stimulation levels of the pulse generator can be programmed relative to a baseline stimulation level, and the patient remote 900 can be configured provide a limited range of selectable stimulation levels either greater than and/or less than the baseline stimulation level, and ideally both. The baseline stimulation level can be selected to correspond to illuminate any one of a plurality of LEDs for the stimulation-level display 910, which can further indicate the number of selectable stimulation levels greater than and less than the baseline stimulation level. In some embodiments, the pulse generator can be programmed to have three selectable stimulation levels greater than the baseline stimulation level and three selectable stimulation levels less than the baseline stimulation level. In such embodiments, when the pulse generator is set to the baseline stimulation level, the fourth LED 910-4 on the patient remote 900 is illuminated (optionally along with first, second, and third LEDs). In other embodiments, the pulse generator can be programmed to have four selectable stimulation levels greater than the baseline stimulation level and two selectable stimulation levels less than the baseline stimulation level. In such embodiments, when the pulse generator is set to the baseline stimulation level, the third LED 910-3 of the patient remote 900 is illuminated (optionally along with first and second LEDs). In alternative aspects, the pulse generator can be programmed such that at the baseline stimulation level, one of the second LED 910-2, the fifth LED 910-5, or the sixth LED 910-6 on the patient remote 900 is illuminated, with corresponding selectable stimulation levels greater than and less than the baseline stimulation level.
Moreover, the baseline stimulation level can be selected to ensure that any adjustment to the therapy via the patient remote remains within a clinically effective range whenever stimulation is applied. In some aspects the clinically effective range of stimulation by the pulse generator can be from about 0.5 mA to about 4 mA. In other aspects, the clinically effective range of stimulation by the pulse generator can be from about 1 mA to about 3 mA. In alternative aspects, the ideal clinically effective range of stimulation by the pulse generator can be from about 0.3 mA to about 2.5 mA, while further for such aspects, stimulation by the pulse generator that is less than 0.3 mA and between from about 2.5 mA to about 4 mA can also be clinically effective at providing treatment. In some embodiments, stimulation is limited to below 4 mA. It is appreciated that the above ranges can be utilized in characterizing and/or programming the neurostimulation device as well. For example, electrodes with stimulation thresholds that provide a desired parameter (e.g. sensory or motor response) an can be categorized as to their suitability for delivering neurostimulation based on which range the threshold lies. For example, in some embodiments, electrodes with a threshold between 0.3-2.5 mA can be considered preferred electrodes for use in neurostimulation therapy delivery, electrodes with thresholds less than 0.3 mA and between 2.5-4 mA can be considered acceptable, and electrodes with thresholds greater than 4 mA can be considered unacceptable for delivering neurostimulation. It is understood that these ranges are an example that is applicable to certain embodiments and certain therapies (e.g. sacral neuromodulation for treatment of OAB and fecal incontinence) and that various other ranges can apply to various other neurostimulation systems and/or therapies.
Accordingly, the baseline stimulation level can be selected to have (1) a pulse amplitude or power within the clinically effective range and (2) a proportional incremental change for increasing or decreasing stimulation relative to the baseline stimulation level such that, at either the maximum or minimum stimulation level selectable via the patient remote, the therapy delivered by the pulse generator remains within the clinically effective range. In further embodiments, the clinically effective range of the pulse generator can include pulses having a pulse amplitude in a range between 0 mA to 1,000 mA, 0 mA to 100 mA, 0 mA to 50 mA, or 0 mA to 25 mA.
In an exemplary embodiment, the pulse generator can be programmed to have a baseline stimulation of 2.0 mA with three selectable stimulation levels greater than the baseline stimulation level and three selectable stimulation levels less than the baseline stimulation level, where each step of adjustment can be ten percent (10%) of the existing or current stimulation level. In such an embodiment, the baseline stimulation level of 2.0 mA is represented in the stimulation-level display 910 by the fourth LED 910-4 being illuminated, the minimum stimulation level selectable by the patient remote 900 is 1.458 mA (represented by the first LED 910-1 being illuminated), and the maximum stimulation level selectable by the patient remote 900 is 2.662 mA (represented by the seventh LED 910-7 being illuminated).
In an alternative exemplary embodiment, the pulse generator can be programmed to have a baseline stimulation of 2.0 mA with four selectable stimulation levels greater than the baseline stimulation level and two selectable stimulation levels less than the baseline stimulation level, where each step of adjustment can be ten percent (10%) of the existing or current stimulation level. In such an embodiment, the baseline stimulation level of 2.0 mA is represented in the stimulation-level display 910 by the third LED 910-3 being illuminated, the minimum stimulation level selectable by the patient remote 900 is 1.62 mA (represented by the first LED 910-1 being illuminated), and the maximum stimulation level selectable by the patient remote 900 is 2.9282 mA (represented by the seventh LED 910-7 being illuminated).
Table 2 set forth below summarizes the functionality resulting from actuation of each of the activation switch 904, the stimulation-increase switch 906, and the stimulation-decrease switch 908, which in some embodiments are in part dependent on the status mode (i.e., awake or asleep) of the patient remote 900. As noted above, when the patient remote 900 is in the asleep mode, both of the stimulation-increase switch 906 and the stimulation-decrease switch 908 are inactive.
In an exemplary implementation, the therapy-remaining display 912 can emit a green light 913g when the pulse generator rechargeable battery has at least thirty percent (>30%) of its charge capacity remaining, which can corresponds to at least four (>4) days of nominal stimulation remaining in the neurostimulation system. Further in this implementation, the therapy-remaining display 912 can emit a constant amber light 913a when the pulse generator battery has more than fifteen percent (>15%) but less than thirty percent (<30%) of its charge capacity remaining, which can corresponds to about two to four (2-4) days of nominal stimulation remaining in the neurostimulation system. The therapy-remaining display 912 emitting a constant amber light 913a can be an indication to the patient that the pulse generator battery is relatively low on charge and requires recharging within the subsequent 2-4 days. Further in this implementation, the therapy-remaining display 912 can emit a flashing amber light 913a when the pulse generator battery has less than fifteen percent (<15%) its charge capacity remaining. The therapy-remaining display 912 emitting flashing amber light 913a can be an indication to the patient that the pulse generator battery is critically low on charge, requires immediate recharging, and that the neurostimulation system may automatically turn off. The therapy-remaining display 912 can further indicate that the pulse generator battery is recharging, where in some aspects the therapy-remaining display 912 can emit a flashing green light 913g as the pulse generator battery recharges.
The amount of charge capacity will vary from battery to battery for any pulse generator or neurostimulation system. In some embodiments, the rechargeable battery can have a charge capacity such that 30% of the charge capacity is about 3.55 Volts and 15% of the charge capacity is about 3.45 Volts, where the therapy-remaining display 912 can emit a constant or flashing green light 913g or a constant or flashing amber light 913a as appropriate relative to such voltages.
The amount of therapy remaining for a neurostimulation system and pulse generator is dependent at least on the duration of usage of the neurostimulation system and the level of stimulation the neurostimulation system is instructed to deliver. Accordingly, a processor coupled to the pulse generator can calculate the amount of therapy remaining in a pulse generator based on factors including, but not limited to, the overall capacity of the pulse generator rechargeable battery, the amount of time elapsed since the pulse generator rechargeable battery was last recharged, the average stimulation level at which the pulse generator is operated, the median stimulation level at which the pulse generator is operated, the current voltage of the battery, and the like. In some aspects, the therapy remaining and/or charge capacity of the pulse generator rechargeable battery can be calculated according to one or more of stimulation amplitude, stimulation frequency, stimulation pulse width, stimulation cycling mode (e.g. duty cycle), and impedance. Based on this calculation, when the patient remote 900 interrogates the neurostimulator and retrieves the status of the pulse generator, the therapy-remaining display 912 can illuminate to provide feedback to the patient indicative of the current amount of therapy remaining in the pulse generator.
The visual indicators of the patient remote 900 can be augmented with a haptic or vibratory feedback that punctuates adjustments to stimulation level, where a vibrating element (e.g., a motor, a piezoelectric, etc.) is disposed within the interior of the portable housing 902. The vibrating element can be configured to activate when the pulse generator confirms that an instruction from the patient remote 900 has been received and executed. Such commands from the patient remote can include, but are not limited to, turning on the pulse generator, turning off the pulse generator increasing the stimulation level of the pulse generator, or decreasing the stimulation level of the pulse generator. The vibration element can also be configured to activate for situations including, but not limited to, the patient remote 900 switching from the asleep mode to the awake mode or providing a warning that the rechargeable pulse generator battery has a low charge.
Table 3 set forth below summarizes the feedback indicators provided in embodiments of the patient remote 900, such as the stimulation-level display 910, the therapy-remaining display 912, and the vibration element, and interpretations of the feedback from the indicators.
The patient remote 900 can further include a fault condition indicator 914, which can illuminate when either or both of the patient remote and the pulse generator are in a fault condition. The fault condition indicator 914 can be an LED, such as a white-light, red-light, or other colored-light LED which can emit a constant or flashing light when either or both of the patient remote and the pulse generator are in a fault condition. Problems with the neurostimulation system that can cause the fault condition indicator 914 to illuminate include, but are not limited to, failure of the pulse generator to respond to commands from the patient remote 900, a low charge for the battery operating the patient remote 900, where fault conditions are of the type common to active implantable devices, which for example may be one or more of low patient remote battery, patient remote software or hardware fault, pulse generator hardware or software fault, and impedance out of range.
In order to make the patient remote 900 a convenient fob device for a patient to carry and used, the portable housing 902 can have a mechanical coupling structure 916 to attach the patient remote 900 with a key ring, karabiner, or other such mounting element. In various aspects, the mechanical coupling structure 916 can be embedded in the structure of the portable housing 902 or looped around a portion of the portable housing 902.
The optional memory 1010 of the patient remote 1000 can store a previous or last stimulation level at which a pulse generator (e.g., an IPG or EPG) paired to the patient remote 1000 was operating. In implementations of the patient remote without an optional memory 1010, the previous or last stimulation level at which a pulse generator paired to the patient remote 1000 was operating can be stored within data memory of the pulse generator, respectively. The status or condition of the pulse generator can be transmitted to the transmission circuitry 1006 of the patient remote 1000 upon interrogation of the pulse generator when the patient remote 1000 is triggered into an awake mode. The status or condition of the pulse generator, particularly the information of the previous or last stimulation level, can be conveyed to the control electronic 1004 of the patient remote to allow for control of the pulse generator via the patient remote based upon the relevant stimulation level of the pulse generator. In many implementations, the transmission of data between a pulse generator and the patient remote can be wireless, and can further be set at a predetermined radio frequency (RF) for a paired set of a patient remote and pulse generator.
In the foregoing specification, the invention is described with reference to specific embodiments thereof, but those skilled in the art will recognize that the invention is not limited thereto. Various features and aspects of the above-described invention can be used individually or jointly. Further, the invention can be utilized in any number of environments and applications beyond those described herein without departing from the broader spirit and scope of the specification. The specification and drawings are, accordingly, to be regarded as illustrative rather than restrictive. It will be recognized that the terms “comprising,” “including,” and “having,” as used herein, are specifically intended to be read as open-ended terms of art.
The present application is a divisional of U.S. patent application Ser. No. 15/969,706, filed on May 2, 2018, entitled “Patient Remote And Associated Methods of Use With A Nerve Stimulation System,” which is a divisional of U.S. patent application Ser. No. 15/861,580, filed on Jan. 3, 2018, entitled “Patient Remote And Associated Methods of Use With A Nerve Stimulation System,” and issued as U.S. Pat. No. 10,105,542 on Oct. 23, 2018, which is a divisional of U.S. patent application Ser. No. 14/992,777, filed on Jan. 11, 2016, entitled “Patient Remote And Associated Methods Of Use With A Nerve Stimulation System,” and issued as U.S. Pat. No. 9,895,546 on Feb. 20, 2018, which claims the benefit of priority to U.S. Provisional Patent Application No. 62/101,666, filed on Jan. 9, 2015, entitled “Patient Remote And Associated Methods Of Use With A Nerve Stimulation System,” the entirety of each which are hereby incorporated by reference herein. The present application is related to U.S. Provisional Patent Application Nos. 62/038,122 filed on Aug. 15, 2014 and entitled “Devices and Methods for Anchoring of Neurostimulation Leads”; 62/038,131, filed on Aug. 15, 2014 and entitled “External Pulse Generator Device and Associated Methods for Trial Nerve Stimulation”; 62/041,611, filed on Aug. 25, 2014 and entitled “Electromyographic Lead Positioning and Stimulation Titration in a Nerve Stimulation System for Treatment of Overactive Bladder, Pain and Other Indicators”; and concurrently filed U.S. Provisional Patent Application Nos. 62/101,888, entitled “Electromyographic Lead Positioning and Stimulation Titration in a Nerve Stimulation System for Treatment of Overactive Bladder” 62/101,899, entitled “Integrated Electromyographic Clinician Programmer For Use With an Implantable Neurostimulator;” 62/101,897, entitled “Systems and Methods for Neurostimulation Electrode Configurations Based on Neural Localization;” 62/101,884, entitled “Attachment Devices and Associated Methods of Use With a Nerve Stimulation Charging Device; and 62/101,782, entitled “Improved Antenna and Methods of Use For an Implantable Nerve Stimulator;” each of which is assigned to the same assignee and incorporated herein by reference in its entirety for all purposes.
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| Number | Date | Country | |
|---|---|---|---|
| 20190321645 A1 | Oct 2019 | US |
| Number | Date | Country | |
|---|---|---|---|
| 62101666 | Jan 2015 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 15969706 | May 2018 | US |
| Child | 16457411 | US | |
| Parent | 15861580 | Jan 2018 | US |
| Child | 15969706 | US | |
| Parent | 14992777 | Jan 2016 | US |
| Child | 15861580 | US |
