Source: https://patents.google.com/patent/US8733363B2/en
Timestamp: 2019-04-26 13:21:28+00:00

Document:
2011-11-16 Assigned to REVENT MEDICAL, INC. reassignment REVENT MEDICAL, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: POUTIATINE, ANDREW, SHADDUCK, JOHN H., TRUCKAI, CSABA, GILLIS, EDWARD M.
A system for treating an airway disorder is provided with an implant body configured to conform to an airway-interface tissue site in a manner compatible with normal physiological function of the site. In some embodiments, the implant body includes an adjustment element configured to allow in-situ adjustment of the implant body between first and second tensioning forces applied to the site. Methods of using such systems are also provided.
This application claims priority to: U.S. Provisional Application No. 61/315,835 filed Mar. 19, 2010; U.S. Provisional Application No. 61/315,838 filed Mar. 19, 2010; U.S. Provisional Application No. 61/347,348 filed May 21, 2010; U.S. Provisional Application No. 61/347,356 filed May 21, 2010; U.S. Provisional Application No. 61/367,707 filed Jul. 26, 2010; U.S. Provisional Application No. 61/418,238 filed Nov. 30, 2010; U.S. Provisional Application No. 61/419,690 filed Dec. 3, 2010.
The invention relates to the field of methods and devices for the treatment of obstructive sleep apnea, and more particularly to opening the airway of subjects with symptoms of obstructive sleep apnea.
Sleep apnea is defined as the cessation of breathing for ten seconds or longer during sleep. During normal sleep, the throat muscles relax and the airway narrows. During the sleep of a subject with obstructive sleep apnea (OSA), the upper airway narrows significantly more than normal, and during an apneic event, undergoes a complete collapse that stops airflow. In response to a lack of airflow, the subject is awakened at least to a degree sufficient to reinitiate breathing. Apneic events and the associated arousals can occur up to hundreds of times per night, and become highly disruptive of sleep. Obstructive sleep apnea is commonly but not exclusively associated with a heavy body type, a consequence of which is a narrowed oropharyngeal airway.
Cyclic oxygen desaturation and fragmented sleeping patterns lead to daytime sleepiness, the hallmark symptom of the disorder. Further consequences of sleep apnea may include chronic headaches and depression, as well as diminished facilities such as vigilance, concentration, memory, executive function, and physical dexterity. Ultimately, sleep apnea is highly correlated with increased mortality and life threatening co morbidities. Cardiology complications include hypertension, congestive heart failure, coronary artery disease, cardiac arrhythmias, and atrial fibrillation. OSA is a highly prevalent disease condition in the United States. An estimated 18 million Americans suffer from OSA to degrees that range from mild to severe, many of whom are undiagnosed, at least in part because the afflicted subjects are often unaware of their own condition.
Treatment of OSA usually begins with suggested lifestyle changes, including weight loss and attention to sleeping habits (such as sleep position and pillow position), or the use of oral appliances that can be worn at night, and help position the tongue away from the back of the airway. More aggressive physical interventions include the use of breathing assist systems that provide a positive pressure to the airway through a mask that the subject wears, and which is connected to a breathing machine. In some cases, pharmaceutical interventions can be helpful, but they generally are directed toward countering daytime sleepiness, and do not address the root cause. Some surgical interventions are available, such as nasal surgeries, tonsillectomy and/or adenoidectomy, reductions in the soft palate, uvula or the tongue base, or advancing the tongue base by an attachment to the mandible and pulling the base forward. These surgical approaches can be quite invasive and thus have a last-resort aspect to them, and further, simply do not reliably alleviate or cure the condition. There is a need for less invasive procedures that show promise for greater therapeutic reliability. There is additional need for the ability to reverse procedures or otherwise revise the procedure, thus allowing for the ability to reverse or otherwise revise the effects of the procedure due to side effects or other undesirable outcomes which may result from the procedure. Additionally, there is the need to do these procedural reversals or revisions in a manner that does not require excessive tissue cutting or invasiveness which can act as a deterrent for patients or physicians to perform such a revision procedure.
The invention relates to a method of alleviating obstructive collapse of airway-forming tissues, and for devices with which to implement the method. Typical patients for whom the method and device may provide therapeutic benefit are those who suffer from obstructive sleep apnea. The method includes implanting a device at a site in the tissue and bioeroding the bioerodible portion of the device to change the shape of the device and to remodel the airway-forming tissue. The implanted device is sized and shaped to conform to the airway-forming tissue site in a manner compatible with normal physiological function of the site; and includes a resiliently deformable portion and a bioerodible portion. In typical embodiments of the method, remodeling the airway-forming tissue results in the airway being unobstructed during sleep, and further, typically, the thus-unobstructed airway diminishes the frequency of apneic events. Remodeling may include reshaping or otherwise altering the position or conformation of airway associated tissue so that its tendency to collapse during sleep is diminished.
The airway is formed from various tissues along its length from the mouth to the lungs. Embodiments of the method include implanting a flexible implant, such as an elastomeric device, into any one or more of these tissues, including, for example, the soft palate, the tongue, generally the base of the tongue, and the pharyngeal walls, typically the posterior and lateral portions of the pharyngeal wall.
In some embodiments, the device is in a deformed shape when implanted, and a bioerodable portion erodes to thereby release a tensioned shape of the implant to apply retraction forces to the site.
With regard to the bioeroding of the bioerodible portion of the device, this may occur over a time span that ranges from days to months. In some embodiments, the bioeroding proceeds at a rate that correlates with the ratio of the biologically-exposed surface area of the bioerodible portion to the volume of the bioerodible portion.
In some embodiments of the method, the bioerosion occurs at a rate that is sufficiently slow for the tissue site to recover from the implanting prior to the device substantially changing shape. In some of these embodiments, the recovery of the tissue site includes a forming of fibrotic tissue around the device, which typically stabilizes the device in the site, and provides the device greater leverage with which to reform the shape of the implant site and its surrounding tissue. In some embodiments, after implanting, and as part of the healing response or recovery from the implantation wound, the newly formed fibrotic tissues infiltrates into holes, pores, or interstices in the device. In some embodiments of the method, a bioactive agent, previously incorporated into the bioerodible material, is released or eluted from the bioerodible portion of the device as it is eroding.
In another aspect of the methods described herein, a method of forming a device to alleviate obstructive collapse of an airway during sleep is provided. The method includes forming a resiliently deformable material into an initial shape that corresponds to the preferred shape of the device, the initial shape having a site for accommodating bioerodible material; changing the initial shape of the resiliently deformable material into a non-preferred shape that is sized and configured into an implantable shape that conforms to an airway-forming tissue site and is compatible with normal physiological function after implantation; and stabilizing the implantable shape by incorporating the bioerodible material into the accommodating site. In some of these method embodiments, changing the initial shape of the resiliently deformable material includes absorbing a force sufficient to remodel the airway as the force is transferred from the device into an implant site after implantation of the device. That level of force is further typically insufficient to remodel the airway to an extent that it is unable to move in a manner that allows substantially normal or acceptable physiological function of the airway.
As noted above, some aspects of the invention further provide a device for alleviating obstruction in an airway, such obstruction typically occurring during sleep. Embodiments of the device include an implantable device sized and shaped to conform to an airway-forming tissue site in a manner compatible with normal physiological function of the site, the device including a resiliently deformable portion and a bioerodible portion. In these embodiments, the resiliently deformable portion has a preferred shape that is constrained in a deformed shape by the bioerodible portion, and the device is configured to return toward the preferred shape of the resiliently deformable portion upon erosion of the bioerodible portion. In some embodiments, the preferred configuration is adapted to remodel the shape of the airway so as to provide a more open airway during sleep.
In typical embodiments of the device, the resiliently deformable portion may include any one or more of a metal or a polymer. In these embodiments, a resiliently deformable metal may include any one or more of stainless steel, spring steel, or superelastic nickel-titanium alloy, and a resiliently deformable polymer may include any one or more of silicon rubber, polyesters, polyurethanes, or polyolefins. In some embodiments, the bioerodible portion may include any one or more of polycaprolactone, polylactic acid, polyglycolic acid, polylactide coglycolide, polyglactin, poly-L-lactide, polyhydroxalkanoates, starch, cellulose, chitosan, or structural protein.
Some embodiments of the device include a portion adapted to engage the tissue into which it is implanted, and in some of these embodiments, the so-adapted portion includes a site for tissue in-growth, such in-growth serving to keep the device and tissue in close proximity, serving to promote implant site remodeling in a manner that conforms to the changing shape of the device. Finally, in some embodiments, the implantable device is configured with sufficient elasticity to allow normal physiological movement around an airway-forming tissue implant site when the device is implanted in the implant site.
In other embodiments, the adapted portion contains sites for tissue to link through the implant after implantation forming tissue plugs which thus form an attachment between the implant and the adjacent tissue without a corresponding adhesion of tissue to the implant. This type of arrangement can produce an implant that can effectively attach to and move tissue while remaining easily removable from the tissue. The tissue plugs can be formed by linking the implant around an encircled mass of tissue or allowing tissue to heal through the implant thus forming the island of encircled tissue. Implants can contain one or more encircled masses of tissue allowing attachment to the adjacent tissue. In some embodiments, a proximal end of the implant is anchored to the patient's mandible and a distal end or ends of the implant is/are releasably anchored to one or more tissue plugs.
FIG. 1 provides an overview of the healthy human airway anatomy, with particular attention to the nasopharyngeal, oropharangeal, and hypopharyngeal regions.
FIG. 2A provides a view of a compromised airway, with an occlusion in the oropharyngeal region due to posterior slippage of the base of the tongue.
FIG. 2B provides a view of a compromised airway with palate closure.
FIG. 3A depicts an elongate implant component of a revisable OSA implant system, the implant having end portions with openings for growth of a tissue plug therethrough to secure the end portions in a treatment site.
FIG. 3B is a cut-away view of an end portion of the implant of FIG. 3A in a tissue site.
FIG. 3C depicts another elongate implant embodiment similar to that of FIG. 3A.
FIG. 3D depicts another elongate implant embodiment.
FIG. 4 depicts another elongate implant corresponding to aspects of the invention.
FIG. 5A depicts a second component of a revisable OSA implant system, the second component comprising a cutting tool.
FIG. 5B depicts the cutting tool of FIG. 5A in a method of use.
FIG. 6 depicts an alternative cutting tool similar to that of FIGS. 5A-5B.
FIG. 7A depicts another elongate implant corresponding to aspects of the invention.
FIG. 7B depicts another elongate implant embodiment.
FIG. 7C depicts another elongate implant embodiment.
FIG. 7D depicts another elongate implant embodiment with multiple openings in multiple planes.
FIG. 7E is a partially cut-away view that depicts an OSA implant with an elastomeric portion that is configured for being releaseably maintained in a tensioned or non-repose condition by a magnesium or magnesium alloy biodissolvable material or element.
FIG. 8A depicts the working end of another embodiment of a cutting tool for cutting a portion of an implant in situ.
FIG. 8B depicts another embodiment of a cutting tool for cutting an implant in a revision procedure.
FIG. 9 depicts another implant with a medial portion having a surface configured for low adhesive energy.
FIG. 10 depicts another elongate implant corresponding to aspects of the invention.
FIG. 11 depicts another implant corresponding to aspects of the invention including a sacrificial portion that can be sacrificed in response to an external stimulus.
FIG. 12 is a cut-away view depicting the implant of FIG. 11 in a tissue site after actuation of the sacrificial portion of the implant.
FIG. 13A depicts an alternative implant including an electrolytically sacrificial portion that can be sacrificed in response to a direct current.
FIG. 13B is a cut-away view depicting the implant of FIG. 13A in a tissue site after actuation of electrolytic connection portion of the implant.
FIG. 14 depicts an end portion of an alternative revisable implant including a cut wire for cutting a tissue plug.
FIG. 15 is a cut-away view depicting the implant of FIG. 14 in a tissue site in the process of actuating the cut wire.
FIG. 16 depicts an end portion of an alternative revisable implant including a cut wire for cutting a plurality of tissue plugs.
FIG. 17 depicts an alternative revisable OSA implant.
FIGS. 18A and 18B illustrate an end portion of the revisable implant of FIG. 17.
FIG. 19 depicts an alternative revisable OSA implant.
FIG. 20 depicts a revisable OSA implant that allows for in-situ post-implant adjustment of the retraction forces applied to tissue by the implant.
FIG. 21 depicts an alternative revisable OSA implant that allows for in-situ post-implant adjustment of the retraction forces.
FIGS. 22 and 23 depict another revisable OSA implant that allows for in-situ post-implant adjustment of the retraction forces.
FIGS. 24A and 24B depict another OSA implant that allows for in-situ post-implant adjustment of the retraction forces.
FIG. 24C depicts another OSA implant with an elongate, linear fluid-tight chamber therein.
FIGS. 25A and 25B depict another OSA implant with a fluid-tight chamber configured for altering fluid volumes therein to adjust retraction forces applied by the implant.
FIG. 26 depicts another OSA implant with an elongate, non-linear fluid-tight chamber therein.
FIG. 27 depicts another OSA implant with an elongate, fluid-tight chamber therein with a sacrificial port.
FIG. 28 depicts an OSA implant with a plurality of fluid-tight chambers therein with sacrificial ports.
FIG. 29 depicts another OSA implant with a plurality of fluid-tight chambers therein with sacrificial ports.
FIG. 30 depicts an OSA implant with a fluid-filled chamber surrounded at least in part by a fluid-permeable wall.
FIGS. 31A and 31B depict an OSA implant with a heat shrink polymer material therein to adjust retraction forces applied by the implant.
FIG. 32 depicts an OSA implant with a shape memory polymer material therein to adjust retraction forces applied by the implant.
FIG. 33 depicts an OSA implant with tooth and ratchet mechanism to adjust retraction forces applied by the implant.
FIGS. 34A and 34B depict an OSA implant with a shape memory alloy frangibolt mechanism therein to adjust retraction forces applied by the implant.
FIG. 1 is a sagittal view of the structures that form the pharyngeal airway 4; some of these structures can become compromised under various conditions to the extent that they obstruct or occlude passage of air through the airway 4, and thus contribute to obstructive sleep apnea. The pharynx is divided, from superior to inferior, into the nasopharynx 1, the oropharynx 2 and the hypopharynx 3. Variations of FIG. 1 are provided in FIGS. 2A and 2B which depict airway obstruction sites 5 at various levels in the pharyngeal airway. FIG. 2A, for example, shows an occlusion 5 at the level of the oropharynx 2, where the base of the tongue 16 and a thickened posterior pharyngeal wall 22 have collapsed against each other. FIG. 2B provides a view of a compromised airway with palate closure. It is also possible for airway obstruction to occur at the level of the nasopharynx 1, where an elongated and/or floppy soft palate can collapse against a thickened posterior pharyngeal wall. Further, an obstruction can occur at the level of the hypopharynx 3, where both an elongated soft palate and a floppy epiglottis 12 can collapse against the pharyngeal wall 22.
With reference to FIGS. 1-2B, the nasopharynx 1 is the portion of the pharynx at the level of or above the soft palate 6. In the nasopharynx, a deviated nasal septum or enlarged nasal turbinates may occasionally contribute to upper airway resistance or blockage. Rarely, a nasal mass, such as a polyp, cyst or tumor may be a source of obstruction. The oropharynx 2 includes structures from the soft palate 6 to the upper border of the epiglottis 12 and includes the inferior surface of the hard palate 14, tongue 16, posterior pharyngeal wall 22 and the mandible 24. The mandible typically has a bone thickness of about 5 mm to about 10 mm anteriorly with similar thicknesses laterally. An obstruction in the oropharynx 2 may result when the tongue 16 is displaced posteriorly during sleep as a consequence of reduced muscle activity during deep or non-REM sleep. The displaced tongue 16 may push the soft palate 6 posteriorly and may seal off the nasopharynx 1 from the oropharynx 2. The tongue 16 may also contact the posterior pharyngeal wall 22, which causes further airway obstruction.
The hypopharynx 3 includes the region from the upper border of the epiglottis 12 to the inferior border of the cricoid cartilage. The hypopharynx 3 further includes the hyoid bone 28, a U-shaped, free-floating bone that does not articulate with any other bone. The hyoid bone 28 is attached to surrounding structures by various muscles and connective tissues. The hyoid bone 28 lies inferior to the tongue 16 and superior to the thyroid cartilage 30. A thyrohyoid membrane and a thyrohyoid muscle attach to the inferior border of the hyoid 28 and the superior border of the thyroid cartilage 30. The epiglottis 12 is infero-posterior to the hyoid bone 28 and attaches to the hyoid bone by a median hyoepiglottic ligament. The hyoid bone attaches anteriorly to the infero-posterior aspect of the mandible 24 by the geniohyoid muscle. Below the hypopharynx 3, the trachea 32 and esophagus 34 are also shown.
FIG. 3A depicts a first component in an exemplary embodiment of a kit or system that provides revisable implants for treating airway disorders or obstructive sleep apnea (OSA). The second component of the exemplary kit is an introducer for insertion into a treatment site as is known in the art and co-pending applications. In FIG. 3A, an elongate device or implant body 100A has first and second end portions 105A and 105B with through-openings 106A and 106B therein. The medial portion 110 of the implant body 100A extends along axis 111 and comprises a biocompatible elastomeric material such as a silicone. The mean cross-section of the medial body portion 110 can range from 1 to 10 mm2 and can be round, oval, flat, polygonal or other suitable shapes. In some embodiments, the elastic modulus of the medial portion can range from 0.5 to 10 MPA and is configured for implanting in the patient's airway tissue in a releasable, tensioned position, as described in co-pending U.S. patent application Ser. No. 11/969,201 which is incorporated herein by this reference.
Referring to FIGS. 3A and 3B, it can be seen that through-openings 106A and 106B in the implant body 100A are configured for growth of a tissue plug 112 through the opening to thereby secure the first and second end portions 105A and 105B in a selected tissue site. The cut-away view of FIG. 3B schematically illustrates that a tissue plug 112 that grows through the opening is thus surrounded or encircled by an encircling body portion 115 of the implant. The encircling body portion 115 comprises a small cross-section element that can be cut, severed, sacrificed, decoupled, or dissolved to disengage the implant from a tissue site 120 as will be described below. The element can be a polymer or other material. In other embodiments described below, the tissue plug 112 can be cut or severed to disengage the implant from the tissue site 120. In one embodiment, the mean cross-section of the tissue plug 112, and thus the dimension across an opening 106A or 106B, can range from about 0.5 mm to 10 mm or more. The openings 106A or 106B can have a round shape in plan view or any other plan shape. The end portions 105A and 105B can have similar or dissimilar configurations, for example an implant configured for treatment of a patient's tongue may have a substantially larger end portion and opening 106B for the base of the tongue and a smaller end portion near the mandible.
FIG. 3C illustrates another implant body 100B with an end portion 105B having an elongated opening 106B through which tissue will grow to form a tissue plug to secure the end portion in the site. For example, the implant body 100B of FIG. 3C has an opening 106B with a primary axis 121 and larger dimension that extends generally orthogonal to the axis 111 of medial portion 110 of the implant body. In use, the greater dimension of the tissue plug will better resist the retraction forces applied to tissue by the elastomeric medial portion 110 of the implant aligned with axis 111.
FIG. 3D depicts another embodiment 100C of a revisable implant for treating an airway disorder that is similar to that of FIG. 3C except the end portion 105B has a through-opening 106B with a terminal part 126 of encircling portion 115 configured with irregular shaped surface features 128 that can interface with the tissue plug that grows through opening 106B. The surface features can comprise undulations, textures, protrusions, bumps and the like that can assist in maintaining the end portion in a fixed position when under the tensioning or retraction forces applied by the medial portion 110 of the implant body 100C. In the implant body 100C of FIG. 3D, the end portion 105B also can have an encircling element 115 that includes a proximal portion 130 of a lower modulus material similar to the modulus of medial portion 110 and the terminal part 126 having a higher modulus to prevent its deformation under tensioning forces.
FIG. 4 depicts another embodiment 100D of a revisable implant that is similar to previous embodiments except that at least one end portion 105B includes an indent feature 140 in the proximal-facing aspect of the encircling portion 115 wherein the indent feature 140 is adapted to direct and receive a cutting blade or edge 144 (phantom view) of a cutting tool for cutting the encircling portion of the implant body to allow its removal from the treatment site. As will be described below (with reference to FIG. 5B), a cutting tool 145 can be advanced along the medial portion 110 of the implant to sever the end portion, which then will allow the entire implant to be withdrawn from the implant site. In another aspect of the invention, the indent feature 140 in the encircling portion 115 can direct the cutting edge 144 to a reduced cross section portion 148 that will require limited force to cut the polymer element with the cutting edge 144.
FIGS. 5A and 5B illustrate a second component of an exemplary kit of a revisable OSA implant system wherein the tool 145 comprises an elongate member with a distal cutting edge 144. One tool embodiment has a passageway 152 extending therethrough for receiving the elongate implant body 100D. In using this tool 145, a first end of the implant body would be freed from tissue or cut and then threaded through the passageway 152. Thereafter, as depicted in FIG. 5B, the tool 145 can be advanced distally while holding the proximal end of the implant to cause the cutting edge 144 to cut across the encircling portion 115. In FIG. 5B, it can be understood how the indent feature 140 and reduced cross section portion 148 (see FIG. 4) direct the cutting edge 144 to easily cut the element to thus release the implant from encircling the tissue plug 112 (cf. FIG. 3B). The tool 145 can be a rigid or semi-rigid member such as a hypotube with a sharpened end. The tool also can be a deflectable, articulatable or steerable member as is known in the art. In another embodiment, the tool can be a flexible plastic material with a blade insert to provide the cutting edge 144. Referring to FIGS. 5B and 3B, it can be understood that the cut end is flexible and can be pulled from around the tissue plug to extract the implant from the site 120 (see FIG. 3B).
FIG. 6 illustrates another second tool component of a revisable implant system wherein the tool 145′ again comprises an elongate member with a distal cutting edge 144. In one embodiment, the tool end includes a longitudinal gap 155 along a side of passageway 152 to thus allow the tool to be inserted over medial portion 110 of an implant body to then advance and cut the implant as depicted schematically in FIGS. 5A-5B. The tool end as shown in FIG. 6 can comprise a polymer member with flexible elements 158 on either side of gap 155 to allow gap 155 to flex open when the device is being inserted over the implant. As depicted, distal cutting edge 144 may comprise a metal blade insert 160 molded into a polymer member.
FIGS. 7A-7C illustrate other embodiments of implants 200A, 200B and 200C that each has a plurality of through-openings 206 in various configurations. In these embodiments, the ends are flat or planar with the openings therein. Thus, in use, there will be a plurality of tissue plugs that grow through the openings 206 to secure the implant ends in the tissue site.
FIG. 7D illustrates another embodiment of implant 200D that has a non-planar end 201 with a plurality of through-openings 202. In one embodiment, the ends have a plurality of elements 204 that extend in different radial angles relative to the axis 111 of the implant with each such element 204 having one or more openings therein.
FIG. 7E illustrates an implant body 200E with ends 205A and 205B and medial portion 206 that comprises an axially-stretched and tensioned elastomeric material. The medial portion 206 is releasably and temporarily maintained in the axially-stretched non-repose condition by a biodissolvable portion, such as of magnesium or magnesium alloy, indicated at 208. In this embodiment, the biodissolvable portion can comprise a tubular member with a foil-like wall or thin-wall, a plurality of thin-wall tube segments, or one or more windings or braids of biodissolvable material. The thin-wall material can be perforated as shown in FIG. 7E. The thin-wall biodissolvable material, or the biodissolvable filament of a winding or braid, can be very fine and adapted to dissolve, erode and/or absorb into the body with a selected time interval ranging from about 2 weeks to 52 weeks. In another embodiment, the biodissolvable portion can be disposed in an interior portion of the implant body, in a linear or helical configuration.
Embodiments of the invention include methods for opening a collapsed or obstructed airway with devices that can be implanted into various tissues that form the airway. Embodiments of the devices include resiliently deformable materials and bioerodible materials. The deformable portion of devices, when first formed, is formed into a preferred shape which is then subsequently deformed, and stabilized in that deformed shape by incorporation or application of bioerodible materials to create a device in its implantable form. Once implanted into a tissue site, and thus exposed to an aqueous environment and subject to cellular and enzymatic action, the bioerodible portions of the device erode, thereby allowing the deformable portion of the device to return toward the preferred form. Embodiments of the method, in their simplest form, thus include implanting a device, the bioerodible portion of the device bioeroding, the device changing shape as a consequence of the bioeroding, and the tissue remodeling in accordance with the force being exerted by the shape changing of the device.
Referring again to FIG. 7E, in operation exemplary device 200E may be implanted into an airway-interface tissue site, such as a patient's tongue. Device 200E is configured with appropriate characteristics, such as its dimensions and flexibility, to be compatible with normal physiological function of the tissue site, such as swallowing and speech. When first implanted, biodissolvable portions 208 maintain medial portion 206 in a stretched configuration. As shown, first and second openings extend through first and second implant ends 205A and 205B, respectively. As the tissue adjacent the implant heals after device 200E is implanted, these openings allow tissue plugs to grow through them, permitting each of the first and second implant ends to surround a tissue plug that forms. This allows the ends of implant 200E to become anchored in the tissue site before portions 208 dissolve and release the stored tension between ends 205A and 205B. Once biodissolvable portions 208 have dissolved and pre-stretched medial portion 206 applies tension between the tissue plugs, the base of the tongue, for example, is drawn in an anterior direction to open a collapsed or obstructed airway. In some embodiments (not shown), the ends of the device may be configured to encircle the tissue plugs upon implantation, without requiring healing time for the tissue plugs to grow through the openings in the ends of the device. Further details of such devices are provided in U.S. provisional application 61/347,356, and further examples of implantation procedures are provided in U.S. application Ser. Nos. 11/969,201 and 12/937,564.
FIG. 8A depicts the working end 210 of an elongated tool that is adapted for cutting an end portion of an implant for its removal, for example an implant of FIG. 3A-3D, 4, or 7A-7D. The tool functions similar to that of FIGS. 5A and 6, wherein the tool has a central bore 212 that receives the elongate medial portion of an implant body. As can be seen in FIG. 8A, the working end 210 includes two concentric hypotubes with a notch 214 therein to push over an end portion 115 of implant 100A of FIG. 3A, for example. The physician can counter-rotate the hypotubes from a proximal handle end wherein blade edges 215 and 216 of the working end function as a scissors mechanism to cut the implant body. Thereafter, the implant can be easily removed from the treatment site. FIG. 8B illustrates another working end 210′ of a similar cutting tool that has opposing notches 214 and 214′ that can receive a implant body portion and blade edges 215 and 216 can be rotated to cut the implant.
FIG. 9 illustrates another embodiment of implant 220 that is similar to any previous embodiment except depicting a difference in surface characteristics of the implant. The end or encircling portion 225 may have smooth or slightly textured surface features and the medial portion 230 may comprise a highly lubricious surface, such as an elastomeric material having an ultra-hydrophobic surface 232 to allow for slippage of the tissue against the implant during use. Thus, a method of the invention comprises implanting a device in airway-interface tissue, securing first and second implant end portions in the tissue by permitting a tissue growth through at least one opening in an end portion, and allowing an elastomeric portion of the implant to apply retraction forces to alleviate tissue obstruction of the airway wherein an ultrahydrophobic surface of the implant prevents tissue adhesion to said surface. Ultrahydrophobic surfaces can be provided in a biocompatible polymer, as is known in the art.
In another aspect of the invention, referring to FIG. 9, the elongate implant body is configured for implanting in an airway-interface and at least a portion of a body surface has a wetting contact angle greater than 70°, to prevent tissue adhesion and to allow tissue slippage. In other embodiments, at least a portion of a body surface has a wetting contact angle greater than 85°, or greater than 100°.
In another aspect of the invention, still referring to FIG. 9, the elongate implant body is configured for implanting in an airway-interface and at least a portion of a body surface has an adhesive energy of less than 100 dynes/cm, less than 75 dynes/cm or less than 50 dynes/cm.
FIG. 10 illustrates another embodiment of revisable OSA implant 250 similar to previous embodiments except the medial portion 252 includes a passageway 254 configured for extending a cutting tool 255 through the passageway for cutting a distal end portion 258 of the implant. The passageway 254 can be accessed by an access opening in the opposing end (not shown) that can be identified by imaging of a marker, visual observation of a marker, by a left-in place guidewire or other suitable means or mechanism. The cutting tool 255 can comprise a scissor member, an extendable blade that is extendable from a blunt-tipped tool, any distal or proximally-facing blade, and/or any type of thermal energy emitter adapted for cutting the implant end 258.
FIG. 11 illustrates another embodiment of revisable OSA implant 280 that has a sacrificial portion indicated at 282 that can be severed or sacrificed by an external stimulus. In one embodiment, a medial portion 283 of the implant includes electrical contacts or extending leads 284A and 284B that can be detachably coupled to an electrical source 285. In FIG. 11, the implant body comprises an elastomeric material as described above and the sacrificial portion 282 comprises a conductively doped polymer portion that acts as a fuse when subject to a very short burst of high voltage RF current. Opposing sides or aspects of the sacrificial portion 282 are coupled to electrical leads 288A and 288B that are embedded or molded into the implant. The use of such doped polymers for a fuse-effect for detachment of endovascular medical implants is disclosed in U.S. Pat. No. 6,458,127 to Truckai et al and issued Oct. 1, 2002, which is incorporated herein by reference. Similar doped polymers can be used in the revisable OSA implant of FIG. 11.
FIG. 12 illustrates a method of using the OSA implant 280 of FIG. 11, and more particularly for revising the treatment. FIG. 12 depicts that an RF current from source 285 has been delivered to melt, sever and sacrifice portion 282 of the implant thus allowing extraction of the implant from around the tissue plug.
FIGS. 13A and 13B illustrate another embodiment of revisable OSA implant 290 that has a sacrificial portion indicated at 282 in a medial portion of the implant that can be actuated and sacrificed by the external stimulus which then leaves the encircling portion 115 of the implant in place. The left-in-place portion of the implant can be used as an anchor for subsequent implants. In one embodiment as in FIGS. 13A-13B, the sacrificial portion 282 can comprise an electrolytic wire that can be sacrificed over a short time interval by direct current as is known in the art. Such electrolytic wire for detachment of embolic coil implants are known in the field of aneurysm implants and treatments.
While FIGS. 11-13B show OSA implants with two forms of sacrificial portions, it should be appreciated that similar implants can have sacrificial portions that are cut, severed or sacrificed by any external stimulus such as RF current, DC current, light energy, inductive heating etc. and may fall within the scope of the invention.
FIGS. 14 and 15 illustrate another embodiment of revisable OSA implant 300 that again includes at least one end with an encircling portion indicated at 315 that encircles a tissue plug 316 that grows through an opening 320. In one embodiment, the implant carries a cut wire 322 that extends in a loop with first and second wire ends 324A and 324B extending through one or more passageways in the implant. The cut wire 322 can be embedded in the surface of the implant surrounding the opening 320. As can be seen in FIG. 15, the looped cut wire 322 can be pulled proximally to cut the tissue plug 316 which then will free the implant from its attachment. In FIG. 14, it can be seen that the cut wire ends 324A and 324B can have a serpentine configuration in the medial portion of the implant so as to not interfere with the tensioning and relaxation of the elastomeric medial implant portion during its use. When the cut wire is accessed and pulled relative to the implant 300, the tissue plug 316 can be cut. It should be appreciated that other tools (not shown) may be used to stabilize the implant when actuating the cut wire as in FIG. 15. The cut wire 322 can be any form of fine wire, or abrasive wire or a resistively heated wire coupled to an electrical source (not shown).
FIG. 16 depicts another revisable OSA implant 300′ that is similar to that of FIGS. 14-15 with the cut wire 322′ configured to cut a plurality of tissue plugs 316 that have grown through openings 320 within an encircling end portion of the implant body.
FIG. 17 depicts another OSA implant 400 that is adapted for revision as previous implants and systems wherein the elongate device or implant body has first and second end portions 405A and 405B with through-openings 406A and 406B therein. The medial portion 411 of implant body 400 extends about an axis and comprises a biocompatible elastomeric material such as a silicone. In this embodiment, the medial portion comprises first and second extending portions 415A and 415B wherein one such portion can be nested in a passageway 416 of the other portion and then form proximal and distal loops or encircling end portions that define openings 406A and 406B for receiving tissue plugs therein. As can be understood from FIGS. 17 and 18A, both the extending portions 415A and 415B comprise an elastomeric material and thus combine to provide the desired retraction forces of the OSA implant.
Referring to FIGS. 18A and 18B, it can be seen that if the second extending portion 415B is cut in a medial or proximal aspect of the implant, or if both the first and second extending portions 415A and 415B are cut in a proximal or medial aspect, then a proximal aspect of the first or outer extending portion 415A can be pulled in the proximal direction and the cut second extending portion 415B then will snake out of the path around the tissue plug 422. Thus, the implant can be cut in a proximal or medial aspect and can be withdrawn from the treatment site from a remote access location.
FIG. 19 depicts another OSA implant 450 that is adapted for a revision procedure and comprises an elongate implant body with first and second end portions 455A and 455B with through-openings 456A and 456B therein. This embodiment is similar to that of FIG. 17 in that medial portion 458 includes extending portions 460A and 460B comprising an elastomeric material that combine to provide the desired retraction forces of the OSA implant. The extending portions 460A and 460B are carried in a thin elastomeric sleeve 464 that has tear-away portions 465 about its ends to prevent tissue ingrowth into the passageway in the sleeve. It can be understood that by cutting the medial portion of the implant, and then pulling on an end of an extending portion 460A or 460B will cause the other free end of the implant to snake around the tissue plug similar to the method depicted in FIG. 18B. Both ends of the implant can be removed from the treatment site by this method.
Another type of OSA implant includes means for in-situ adjustment of force applied by the implant after implantation in the treatment site. Such an adjustment can increase or decrease the applied forces applied to the treatment site by the implant. Such adjustment of forces applied by the implant typically may be performed upon specific event, such as periodic evaluations of the treatment. The adjustment also can be done at a pre-determined schedule, based on an algorithm, or can be random. In one example, the patient may gain or lose weight which could result in a need for adjusting the forces applied by the implant. Other influences can be a worsening of the patient's condition, the aging of the patient, local tissue remodeling around the implant, age of the implant or degradation of material properties of the implant. In some embodiments described below, an implant system can be provided that is easily adjustable in-situ between first and second conditions on a repetitive basis, for example, that can be adjusted for sleep interval and for awake intervals on a daily basis. Such an adjustable embodiment can thus deliver tissue-retraction forces only when needed during sleep. One advantage of such an embodiment would be to allow the tissue of the treatment site to be free from implant-generated retraction forces during awake intervals to prevent or greatly limit the potential of tissue remodeling due to a continuous application of such retraction force.
FIG. 20 depicts a revisable OSA implant 500 that is adapted for minimally invasive in-situ post-implant adjustment of retraction forces applied by the implant. In this embodiment, the implant is configured for a downward adjustment of retraction forces applied by the OSA implant. In FIG. 20, it can be seen that the elongate implant body has a plurality of extending elements 502 coupled to end portion 505, wherein the elements 502 can be individually cut to reduce the applied retraction forces of the implant. The number of extending elements 502 can range from 2 to 20 or more.
FIG. 21 depicts a revisable OSA implant 520 that functions as the previous embodiment except that the plurality of extending elements 502 are housed in thin-wall elastomeric sleeve 522. Further, an axial portion 525 of some or each extension element 502 protrudes outward from sleeve 522, or an end portion 530 of the implant, to allow such a portion to be cut. Soft filler or “tear away” material 532, such as a very low modulus silicone, may be provided around each extension element 502 where it protrudes from sleeve 522 to prevent tissue ingrowth into the interior channels of the device. In use, a physician is able to pick up the elastic element 502 and cut it, and filler material 532 just tears away in the process. Again, any foam of cutting tool can be used for minimally invasive access to cut an elastomeric element to titrate retraction forces in a downward direction.
FIG. 22 depicts an OSA implant 600 that is adapted for in-situ post-implant adjustment of retraction forces applied to targeted tissue. In one method, assume that it is desirable to increase the applied retraction forces over time due to tissue remodeling wherein greater retraction forces are desired. In FIG. 22, the elongated implant body has a medial portion 606 that includes an interior channel 610 that extends from an accessible first end 612 to a remote end 615. Each end 612 and 615 can include a silicone membrane to prevent tissue ingrowth but will allow a needle to be inserted therethrough. The channel ends 612 and 615 can be disposed in more rigid end portions of the implant, wherein the medial portion of the implant body comprises an elastomer to provide the desired retraction forces. In one embodiment, the channel 610 is dimensioned to collapse or flatten but can also accommodate the insertion of at least one additional elastomeric element indicated at 620. It can be understood from FIG. 23 that an elastomeric element 620 with end-toggles 624 can be inserted in a bore of a flexible needle member (not shown) and inserted through the channel in the implant so that the toggles are released to deploy the element 620 in a tensioned position to thereby add to the retraction forces applied to tissue collectively with the medial portion 606 of the implant 600. In a similar manner, an end of the implant 600 and/or elastomeric element 620 can be clipped to reduce the applied retraction forces as in the system and method depicted in FIGS. 20 and 21.
Thus, in general, the system and implants of FIGS. 20-23 corresponding to aspects of the invention comprise an elongate implant sized and shaped to conform to an airway-interface tissue site in a manner compatible with normal physiological function of the site, a medial portion of the implant comprising an elastomeric material configured to apply retraction forces to the site, and adjustment means for in situ adjustment of retraction forces applied by the implant.
FIGS. 24A and 24B are schematic views of another embodiment of an in-situ adjustable implant that allows for adjustment of applied force. In FIG. 24A, an elastomeric implant body 700 has first and second end portions 705A and 705B with a medial portion 710 that can be temporarily maintained in an extended or stretched non-repose position by at least one bioerodible or biodissolvable element or segment, for example segments indicated at 712 a-712 d as described in co-pending application Ser. No. 11/969,201. The medial portion of the implant further comprises a cylindrical reservoir or chamber 715 enclosed within walls 718 that can carry a liquid, gel or gas media 720 that can be increased in volume or decreased in volume to alter the effective length of L of the implant medial portion 710 after the portions 705A and 705B have been secured in the tissue site. In one embodiment, the reservoir 715 has exterior walls 718 fabricated of an elastomeric material and configured with a helically woven material or helical spring 724 that allows for the walls 718 to stretch and contract axially without substantial change in the cross section of the reservoir within the walls 718. FIG. 24B shows the implant medial portion 710 of implant 700 with altered length L′. In one aspect of a method of the invention, as depicted in FIG. 24B, the in-situ implant can be accessed with a needle 730 tip that can penetrate the elastomeric wall 718. The implant can carry at least one marker 732 such as radiopaque marker(s) to allow the physician to insert to needle precisely into the reservoir. The material of the elastomeric wall 718, such as silicone (e.g. materials as described in U.S. patent application Ser. No. 11/969,201) has a thickness and modulus that provides for self-sealing after the needle tip 730 is withdrawn. In one embodiment, the liquid media 720 can comprise a biocompatible silicone oil or saline solution. In another embodiment of FIG. 24C, the reservoir 715 can extend over any part of medial portion 710 such as over the entire length of the medial portion 710, with a port indicated at 732. The wall 718 of the implant body is configured for axial stretching upon pressurizing the chamber 715 and configured for resisting radial expansion under such pressure. In another embodiment, the reservoir 715 can be enclosed in a bellows-like structure (not shown). In another embodiment, a gas may be used such as CO2, nitrogen, argon or another biocompatible gas. It thus can be understood that increasing the effective length L of the implant can reduce forces applied by the implant. Alternatively, decreasing the effective length of the implant can increase forces applied by the implant.
FIGS. 25A and 25B depict an alternative embodiment 735 wherein the targeted needle port region 736 adapted for access with a needle is remote from the fluid reservoir or chamber 715, for example in an opposing axially-extending region 740 of the implant. The needle port region 736 is in fluid communication with chamber 715 via lumen 742 extending through region 744. The configuration of FIG. 25A is suited for treatment sites wherein one end of the implant is more accessible to a needle tip 730. As can be seen in FIGS. 25A-25B, the reservoir or chamber 715 comprises a lumen portion in region 740 of the implant which in a first condition is free of a fluid thus allowing the region to apply forces based on the elastomeric material of the implant. To adjust the forces applied by the implant, an incompressible fluid 720 can be injected into the implant which will occupy the chamber 715 thus preventing the elastomeric material of the implant in region 740 from applying forces to tissue, at the same time as allowing the remainder of the elastomeric material to apply forces to the treatment site. It can be appreciated that the implant may be implanted with the chamber 715 in region 740 filled with a fluid, and the adjustment comprises utilizing the needle tip 730 to extract fluid from the implant or add additional fluid to the implant. As can be seen in FIG. 25A, to insure that the incompressible fluid 720 in region 744 does not impinge significantly on the function of the elastomeric in said portion 744, the lumen 742 is non-axial or non-linear with respect to the implant 735, but rather is helical, convoluted, zigzag or the like which would still allow the elastomeric portion to function without having to apply forces directly on an axially-extending chamber filled with an incompressible fluid.
FIG. 26 depicts an alternative embodiment 770 of in-situ adjustable implant body having an elastomeric medial region 772 for applying forces to tissue. The medial region 722 again includes at least one interior chamber 775 filled with a fluid, for example a biocompatible fluid such as saline 720, that is filled under pressure with the implant body in a stretched condition. In this embodiment, the chamber 775 comprises a non-linear lumen, such as a helical lumen, that can be filled with an incompressible fluid or the fluid can be released from the lumen. It can be understood that if the helical lumen is fluid-filled, the elastomeric material can still apply retraction forces after being disposed in a treatment site, but the fluid 720 will lessen or dampen the applied forces provided by the implant. If the fluid 720 is evacuated from the lumen 775, then the elastomeric portion will apply retraction forces without being impinged by the fluid. FIG. 26 depicts a needle tip 730 puncturing a port region 776 overlying the fluid chamber 775 which thus allows the biocompatible fluid to escape into the treatment site. Alternatively, the fluid can be extracted through the needle tip 730. A similar implant body can be configured with an elongated fluid-filled linear lumen that would restrict movement of the elastomeric body around the linear lumen as in the implant of FIG. 24C.
FIG. 27 illustrates another similar embodiment 770′ except that the implant includes a sacrificial seal or port 777 that can be sacrificed or dissolved by application of energy from a remote energy source 780 so that a tool does not need to be penetrated into the treatment site. In one embodiment, an electrical source 780 can inductively heat a conductively doped polymer that comprises the seal 777 to melt the seal and thus release the biocompatible fluid. In another embodiment, light energy that produces a wavelength sufficient to heat a sacrificial seal may be used, or a coil may be provided in the implant that is responsive to electrical energy to create a current in the implant to sacrifice the seal 777.
FIG. 28 depicts another similar embodiment 780 wherein the implant carries a plurality of non-linear lumens 782A and 782B that each are filled with an incompressible fluid 720 that can be released independently through a seal 785A or 785B such as by any means described above to adjust the retraction forces applied by the implant. In the implant of FIG. 28, two helically-configured lumens 782A and 782B that overlap are shown, but the plurality of lumens can range from 2 to 10 or more and comprise axially overlapping lumens, partly overlapping lumens or non-overlapping lumens.
FIG. 29 depicts an implant embodiment 790 similar to that of FIG. 28 wherein the implant 790 again carries a plurality of lumens 792A-792C that are both non-linear (helical) and linear—each within elastomeric, axial-extending regions 795A-795C, respectively. In this embodiment, it can be understood that each linear lumen 792B, 792C is filled with an incompressible fluid 720 that maintains the associate discrete region 795B, 795C in a stretched condition when the implant 790 resides in a treatment site. Thus, the fluid 720 in each region is adapted to prevent said regions 795B, 795C from applying retraction forces to tissue until the time that a sacrificial port or seal 796B or 796C is opened to allow one or more lumens to be freed of fluid 720. The seals or ports can be opened, for example by any means described above, to thus adjust the retraction forces applied by the implant.
FIG. 30 depicts an alternative embodiment 800 that is similar to those described above except a permeable wall 802 surrounding the fluid-filled interior chamber 805 can be slightly permeable to allow a controlled migration of fluid 720 from the chamber to thus allow the elastomeric material to apply greater retraction forces to the tissue. The interior chamber or chambers can be non-linear or linear to thus function as described previously to permit the implant to increase retraction forces applied by implant to the treatment site.
In another embodiment, an implant similar to that of FIG. 30 can have an interior chamber filled with a salt and moisture absorbed through the slightly permeable wall can cause the salt to dissolve which will change the forces applied by the implant, typically to reduce the forces applied by the implant.
FIGS. 31A-31B depict another implant embodiment 820 that has first and second end portions 825A and 825B with openings therein configured for securing in a treatment site with tissue plugs as describe previously. In this embodiment, the medial portion 826 of implant 820 includes an elastomeric portion 830 that applies retraction forces to tissue as described in previous embodiments. The medial portion 826 of the implant further includes an adjustable non-elastomeric portion 835 that comprises a heat-shrink polymer that can be shortened upon heating. In one embodiment, the heat shrink material 835 can comprise a conductively-doped heat-shrink polymer that can be inductively heated to thereby increase in temperature cause its shrinkage and adjust upwardly the forces applied by the implant to the engaged tissue. FIG. 31B shows the medial portion 826 of the implant being shortened by actuation of the heat shrink material 835.
FIG. 32 depicts another implant 840 with end portions 845A and 845B with openings configured for growth of tissue plugs therethrough as described previously. The implant can function in a manner similar to that of FIGS. 31A-31B. In implant 840 of FIG. 32, the implant has a medial portion 846 comprising at least in part a shape memory polymer (SMP). By the term shape memory polymer, it is meant that the polymer demonstrates the phenomena of shape memory based on the fabrication of a body comprising a segregated linear block co-polymer, typically of a hard segment and a soft segment. The shape memory polymer generally is characterized as defining phases that result from glass transition temperatures (Tg) in the hard and soft segments or other types of phase change. The hard segment of SMP typically is crystalline with a defined melting point, and the soft segment is typically amorphous, with another defined transition temperature. In some embodiments, these characteristics may be reversed together with the segment's glass transition temperatures. The SMP portion 850 of the implant body can be fabricated to an initial extended (temporary) memory shape. In such an embodiment, when the SMP material is elevated in temperature above the melting point or glass transition temperature of the hard segment, the material is then formed into its memory shape. The selected shape is memorized by cooling the SMP below the melting point or glass transition temperature of the hard segment. When the shaped SMP is cooled below the melting point or glass transition temperature of the soft segment while the shape is deformed, that temporary shape is fixed. The temporary shape can comprise an extended shape, a non-extended shape or any other shape for implanting in a treatment site.
The original memory shape is recovered by heating the material above the melting point or glass transition temperature Tg of the soft segment but below the melting point or glass transition temperature of the hard segment. (Other methods for setting temporary and memory shapes are known which are described in the literature below). The recovery of the original memory shape is thus induced by an increase in temperature, and is termed the thermal shape memory effect of the polymer. The transition temperature can be body temperature or somewhat below 37° C. for a typical embodiment. Alternatively, a higher transition temperature can be selected and a remote source can be used to elevate the temperature and change the SMP structure to its memory shape (i.e., inductive heating or light energy absorption). Referring to FIG. 32, the shape memory polymer portion of the implant can be conductively doped to allow for inductive heating, or an inductively heated material may comprise a jacket around the SMP or be embedded in the SMP. Thus, heating the SMP can cause a change in its length to a greater length or less length.
The SMP component 850 of the implant of FIG. 32 can also be used to directly adjust another parameter of the implant 840 to alter applied forces, other than the length of the implant. In other words, the thermal shape memory effect of the polymer can be configured to provide a memorized physical property of the SMP portion which can be controlled by its change in temperature or stress, for example the parameter can comprise the elastic modulus, hardness, flexibility or permeability. Examples of polymers that can be utilized in the hard and soft segments of SMPs include polyurethanes, polynorborenes, styrene-butadiene co-polymers, cross-linked polyethylenes, cross-linked polycyclooctenes, polyethers, polyacrylates, polyamides, polysiloxanes, polyether amides, polyether esters, and urethane-butadiene co-polymers and others identified in the following patents and publications: U.S. Pat. No. 5,145,935 to Hayashi; U.S. Pat. No. 5,506,300 to Ward et al.; U.S. Pat. No. 5,665,822 to Bitler et al.; and U.S. Pat. No. 6,388,043 to Langer et al.; Mather, Strain Recovery in POSS Hybrid Thermoplastics, Polymer 2000, 41(1), 528; Mather et al., Shape Memory and Nanostructure in poly(norbornyl-POSS) Copolymers, Polym. Int. 49, 453-57 (2000); Lui et al., Thermomechanical Characterization of a Tailored Series of Shape Memory Polymers, J. App. Med. Plastics, Fall 2002.
FIG. 33 depicts another embodiment of OSA implant 900 that is adapted for implantation with a first extended length X and thereafter can be actuated to move the implant toward a second less extended length. In one embodiment and method of the invention, the implant 900 is implanted in a treatment site such as a patient's tongue. According to the method of adjustment, rather than accessing the implant with a tissue-penetrating tool, the implant 900 of FIG. 33 is configured to be shortened by physical manipulation of the tongue by gripping the exterior of the tongue with fingers or a suitable jig or device to move a first component 905 of the implant 900 relative to a second component 906 wherein a slightly flexible tooth mechanism 908 is configured to grip one of a series of tooth-engaging elements 910. It can be understood that regions 912 and/or 914 can comprise an elastomeric portion of the implant, and that the tooth mechanism comprises an independent length adjustment mechanism. The system also can include any latch mechanism or the like that can be manipulated manually to alter the forces applied by the implant.
It should be appreciated that the method of manipulating the exterior of the tongue to actuate a force-receiving mechanism carried by the implant body can be utilized in implants in any airway-interface tissue described above. In another system and method embodiment, the patient can utilize such external manipulation to actuate a fluid-filled implanted squeeze bulb component carried by the implant body, or separated from but communicating with the implant body, to move a fluid into or out of a chamber in an implant body to adjust forces applied by an implant body as described above. The chamber of the implant body can include a leaky valve to slowly allow the biocompatible fluid to return to the bulb over a time interval such as any planned sleep interval. In another embodiment, the system can have first and second squeeze bulbs to allow for manipulation to move the fluid into the chamber in the implant body and the out of the chamber in the implant body, respectively. A system for moving fluid into and out of a chamber of an OSA implant also can be operatively coupled to a pump known in the art for pumping the fluid in a microchannel of the implant, with the pump stimulated by a remote energy source. In this embodiment, the implant thus can be adjusted by the patient following implantation between first and second conditions on a repetitive basis, in one example, for greater applied retraction forces during a sleep interval and for lesser or no applied forces during awake intervals.
FIGS. 34A and 34B depict another embodiment of OSA implant 920 that is adapted for implantation with a non-extended length X and thereafter can be actuated to move the implant toward a second extended length X′. In one embodiment and method of the invention, the medial portion 925 of the implant comprises an elastomeric material that is axially compressed along axis 930 and releaseably maintained in the axially compressed condition by an elongate tension element 932 carried by the medial portion. The tension element further carries release means indicted at 935 which can comprise a sacrificial element of frangible material that releases first end portion 936A of the tension element 932 from the second end portion 936B of element 932. In one embodiment, the release mechanism comprises a miniature frangibolt which comprises a shape memory alloy sleeve, such as a nickel titanium alloy sleeve, which instantly elongates after reaching a certain temperature. That trigger temperature may be achieved by a heater that is disposed about the sleeve. In this embodiment, the sleeve expands a predetermined amount between surrounding collars upon heating which breaks a wire element. In the embodiment of FIG. 34A-34B, the NiTi sleeve can be heated by an inductively-heated doped polymer that responds to an alternating electric field (FIG. 34B). In another embodiment, the release element can comprise a sacrificial or fuse-like polymer portion that is sacrificial upon a selected voltage passed through such a release element as described in other embodiments above. While the tension member 932 in FIG. 34A is shown releasably maintaining the implant in an axially-compressed condition, it should be appreciated that such a tension element or compression element with a frangible or sacrificial element can also be use to releasably maintain an elastomeric implant in an axially-extended condition for implantation in a treatment site.
The embodiments of implants shown in the figures above can be sized and shaped to conform to a treatment site in a patient's tongue, palate or other site in airway-interface tissue and to reside in an orientation and in a manner compatible with normal physiological function of the site. The overall dimensions may vary according to the full extent that human subjects vary in their anatomical dimensions, and thus the dimensions provided here are only an approximation for the purpose of illustration, and are not meant to be limiting. Any embodiment in its elongated state may typically be in the range of about 2 cm to about 10 cm in length in a releasably extended state, and the implant in a contracted state may be in the range of about 1 cm to about 6 cm in length.
Unless defined otherwise, all technical terms used herein have the same meanings as commonly understood by one of ordinary skill in the art to which this invention belongs. Specific methods, devices, and materials are described in this application, but any methods and materials similar or equivalent to those described herein can be used in the practice of the present invention. While embodiments of the inventive device and method have been described in some detail and by way of exemplary illustrations, such illustration is for purposes of clarity of understanding only, and is not intended to be limiting.
Various terms have been used in the description to convey an understanding of the invention; it will be understood that the meaning of these various terms extends to common linguistic or grammatical variations or forms thereof. It will also be understood that when terminology referring to devices or equipment has used trade names, brand names, or common names, that these names are provided as contemporary examples, and the invention is not limited by such literal scope. Terminology that is introduced at a later date that may be reasonably understood as a derivative of a contemporary term or designating of a subset of objects embraced by a contemporary term will be understood as having been described by the now contemporary terminology.
While some theoretical considerations have been advanced in furtherance of providing an understanding of the invention the claims to the invention are not bound by such theory. Described herein are ways that embodiments of the invention may engage the anatomy and physiology of the airway, generally by opening the airway during sleep; the theoretical consideration being that by such opening of the airway, the implanted device embodiments alleviate the occurrence of apneic events. Moreover, any one or more features of any embodiment of the invention can be combined with any one or more other features of any other embodiment of the invention, without departing from the scope of the invention. Further, it should be understood that while these inventive methods and devices have been described as providing therapeutic benefit to the airway by way of intervention in tissue lining the airway, such devices and embodiments may have therapeutic application in other sites within the body, particularly luminal sites. Still further, it should be understood that the invention is not limited to the embodiments that have been set forth for purposes of exemplification, but is to be defined only by a fair reading of claims that are appended to the patent application, including the full range of equivalency to which each element thereof is entitled.
an adjustment element in the implant body configured to allow in-situ adjustment of the implant body between first and second tensioning forces applied to the site, wherein the implant body includes a ratchet mechanism allowing adjustment between said first and second tensioning forces.
2. The system of claim 1 wherein the implant body includes a modifiable polymer configured to provide adjustment between said first and second tensioning forces.
wherein the manipulating step is accomplished by manipulating the tongue surface wherein manipulating the tongue surface adjusts a latch mechanism in the implant body and further wherein the latch mechanism comprises a ratcheting member.
US1107992A (en) * 1914-01-26 1914-08-18 John E Parrish Broadcasting mechanism.
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