U.S. patent application number 14/275426 was filed with the patent office on 2014-09-04 for systems and methods for treatment of sleep apnea.
The applicant listed for this patent is Edward M. GILLIS, Andrew POUTIATINE, John H. SHADDUCK, Csaba TRUCKAI. Invention is credited to Edward M. GILLIS, Andrew POUTIATINE, John H. SHADDUCK, Csaba TRUCKAI.
Application Number | 20140246027 14/275426 |
Document ID | / |
Family ID | 46272859 |
Filed Date | 2014-09-04 |
United States Patent
Application |
20140246027 |
Kind Code |
A1 |
GILLIS; Edward M. ; et
al. |
September 4, 2014 |
SYSTEMS AND METHODS FOR TREATMENT OF SLEEP APNEA
Abstract
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.
Inventors: |
GILLIS; Edward M.;
(Livermore, CA) ; POUTIATINE; Andrew; (Mill
Valley, CA) ; SHADDUCK; John H.; (Menlo Park, CA)
; TRUCKAI; Csaba; (Saratoga, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
GILLIS; Edward M.
POUTIATINE; Andrew
SHADDUCK; John H.
TRUCKAI; Csaba |
Livermore
Mill Valley
Menlo Park
Saratoga |
CA
CA
CA
CA |
US
US
US
US |
|
|
Family ID: |
46272859 |
Appl. No.: |
14/275426 |
Filed: |
May 12, 2014 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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13053059 |
Mar 21, 2011 |
8733363 |
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14275426 |
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61315835 |
Mar 19, 2010 |
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61315838 |
Mar 19, 2010 |
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61347348 |
May 21, 2010 |
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61347356 |
May 21, 2010 |
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61367707 |
Jul 26, 2010 |
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61418238 |
Nov 30, 2010 |
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61419690 |
Dec 3, 2010 |
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Current U.S.
Class: |
128/848 |
Current CPC
Class: |
A61F 5/56 20130101; A61F
2210/0004 20130101; A61F 2/00 20130101; A61F 5/566 20130101 |
Class at
Publication: |
128/848 |
International
Class: |
A61F 5/56 20060101
A61F005/56 |
Claims
1. A system for treating an airway disorder, comprising: an implant
body having an axis and sized and shaped to conform to an
airway-interface tissue site in a manner compatible with normal
physiological function of the site; and 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.
2. The system of claim 1 wherein the implant body includes a fluid
containment chamber allowing adjustment between said first and
second tensioning forces.
3. The system of claim 1 wherein the implant body has an axial
passageway configured to receive a tension element.
4. The system of claim 1 wherein the implant body includes a
modifiable polymer configured to provide adjustment between said
first and second tensioning forces.
5. A system for treating an airway disorder, comprising: an implant
body having an axis and sized and shaped to conform to an
airway-interface tissue site in a manner compatible with normal
physiological function of the site; and an axial passageway in the
implant body configured to receive a tension element.
6. The system of claim 5 further comprising a tool for introducing
the tensioning element into the axial passageway.
7. A method of treating an airway disorder, comprising: implanting
an elongate implant body into a site in a patient's tongue, the
implant sized and shaped to conform in a manner compatible with
normal physiological function of the site and to apply selected
tensioning forces to the site; manipulating the implant in situ to
alter the tensioning forces applied to the site.
8. The method of claim 7 wherein the manipulating step is performed
after at least end portions of the implant body are secured in the
tissue.
9. The method of claim 7 wherein the implant body comprises an
elastomeric material that applies the selected tensioning
forces.
10. The method of claim 7 wherein the manipulating step is
accomplished with a tool that accesses the site.
11. The method of claim 10 wherein the tool is configured to
decouple portions of the implant body.
12. The method of claim 10 wherein the tool is configured to add a
tensioning element to the implant body.
13. The method of claim 7 wherein the manipulating step is
accomplished by stimulus means remote from the implant body.
14. The method of claim 7 wherein the manipulating step is
accomplished by manipulating the tongue surface.
15. The method of claim 14 wherein manipulating the tongue surface
adjusts a latch mechanism in the implant body.
16. The method of claim 15 wherein the latch mechanism comprises a
ratcheting member.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a divisional of U.S. application Ser.
No. 13/053,059 filed Mar. 21, 2011, which claims the benefit of
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.
INCORPORATION BY REFERENCE
[0002] All publications, patents and patent applications mentioned
in this specification are herein incorporated by reference to the
same extent as if each individual publication, patent or patent
application was specifically and individually indicated to be
incorporated by reference.
FIELD OF THE INVENTION
[0003] 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.
BACKGROUND OF THE INVENTION
[0004] 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.
[0005] 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.
[0006] 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 hack 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.
SUMMARY OF THE INVENTION
[0007] 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.
[0008] 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.
[0009] 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.
[0010] 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.
[0011] 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.
[0012] 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.
[0013] 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.
[0014] 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.
[0015] 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.
[0016] 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.
BRIEF DESCRIPTION OF THE DRAWINGS
[0017] FIG. 1 provides an overview of the healthy human airway
anatomy, with particular attention to the nasopharyngeal,
oropharangeal, and hypopharyngeal regions.
[0018] 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.
[0019] FIG. 2B provides a view of a compromised airway with palate
closure.
[0020] 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.
[0021] FIG. 3B is a cut-away view of an end portion of the implant
of FIG. 3A in a tissue site.
[0022] FIG. 3C depicts another elongate implant embodiment similar
to that of FIG. 3A.
[0023] FIG. 3D depicts another elongate implant embodiment.
[0024] FIG. 4 depicts another elongate implant corresponding to
aspects of the invention.
[0025] FIG. 5A depicts a second component of a revisable OSA
implant system, the second component comprising a cutting tool.
[0026] FIG. 5B depicts the cutting tool of FIG. 5A in a method of
use.
[0027] FIG. 6 depicts an alternative cutting tool similar to that
of FIGS. 5A-5B.
[0028] FIG. 7A depicts another elongate implant corresponding to
aspects of the invention.
[0029] FIG. 7B depicts another elongate implant embodiment.
[0030] FIG. 7C depicts another elongate implant embodiment.
[0031] FIG. 7D depicts another elongate implant embodiment with
multiple openings in multiple planes.
[0032] 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.
[0033] FIG. 8A depicts the working end of another embodiment of a
cutting tool for cutting a portion of an implant in situ.
[0034] FIG. 8B depicts another embodiment of a cutting tool for
cutting an implant in a revision procedure.
[0035] FIG. 9 depicts another implant with a medial portion having
a surface configured for low adhesive energy.
[0036] FIG. 10 depicts another elongate implant corresponding to
aspects of the invention.
[0037] 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.
[0038] 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.
[0039] FIG. 13A depicts an alternative implant including an
electrolytically sacrificial portion that can be sacrificed in
response to a direct current.
[0040] 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.
[0041] FIG. 14 depicts an end portion of an alternative revisable
implant including a cut wire for cutting a tissue plug.
[0042] 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.
[0043] FIG. 16 depicts an end portion of an alternative revisable
implant including a cut wire for cutting a plurality of tissue
plugs.
[0044] FIG. 17 depicts an alternative revisable OSA implant.
[0045] FIGS. 18A and 18B illustrate an end portion of the revisable
implant of FIG. 17.
[0046] FIG. 19 depicts an alternative revisable OSA implant.
[0047] 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.
[0048] FIG. 21 depicts an alternative revisable OSA implant that
allows for in-situ post-implant adjustment of the retraction
forces.
[0049] FIGS. 22 and 23 depict another revisable OSA implant that
allows for in-situ post-implant adjustment of the retraction
forces.
[0050] FIGS. 24A and 24B depict another OSA implant that allows for
in-situ post-implant adjustment of the retraction forces.
[0051] FIG. 24C depicts another OSA implant with an elongate,
linear fluid-tight chamber therein.
[0052] 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.
[0053] FIG. 26 depicts another OSA implant with an elongate,
non-linear fluid-tight chamber therein.
[0054] FIG. 27 depicts another OSA implant with an elongate,
fluid-tight chamber therein with a sacrificial port.
[0055] FIG. 28 depicts an OSA implant with a plurality of
fluid-tight chambers therein with sacrificial ports.
[0056] FIG. 29 depicts another OSA implant with a plurality of
fluid-tight chambers therein with sacrificial ports.
[0057] FIG. 30 depicts an OSA implant with a fluid-filled chamber
surrounded at least in part by a fluid-permeable wall.
[0058] FIGS. 31A and 31B depict an OSA implant with a heat shrink
polymer material therein to adjust retraction forces applied by the
implant.
[0059] FIG. 32 depicts an OSA implant with a shape memory polymer
material therein to adjust retraction forces applied by the
implant.
[0060] FIG. 33 depicts an OSA implant with tooth and ratchet
mechanism to adjust retraction forces applied by the implant.
[0061] FIGS. 34A and 34B depict an OSA implant with a shape memory
alloy frangibolt mechanism therein to adjust retraction forces
applied by the implant.
DETAILED DESCRIPTION OF THE INVENTION
A. Anatomy of the Pharynx
[0062] 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.
[0063] 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.
[0064] 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.
B. Revisable OSA Implants
[0065] 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
mm.sup.2 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.
[0066] 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.
[0067] 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.
[0068] 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.
[0069] 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.
[0070] 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).
[0071] 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.
[0072] 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.
[0073] 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.
[0074] 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.
[0075] 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.
[0076] 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.
[0077] 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.
[0078] 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.
[0079] 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.degree., 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.degree., or greater than 100.degree..
[0080] 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.
[0081] 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.
[0082] 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.
[0083] 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.
[0084] 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.
[0085] 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.
[0086] 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).
[0087] 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.
[0088] 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.
[0089] 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.
[0090] 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.
C. In-Situ Adjustable Force OSA Implants
[0091] 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.
[0092] 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.
[0093] 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 form of cutting tool can be used for
minimally invasive access to cut an elastomeric element to titrate
retraction forces in a downward direction.
[0094] 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.
[0095] 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.
[0096] 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 712a-712d 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 CO.sub.2, 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.
[0097] 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.
[0098] 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.
[0099] 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.
[0100] 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.
[0101] 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.
[0102] 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.
[0103] 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.
[0104] 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.
[0105] 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.
[0106] The original memory shape is recovered by heating the
material above the melting point or glass transition temperature
T.sub.g 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.degree. 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.
[0107] 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.
[0108] 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.
[0109] 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.
[0110] 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.
[0111] 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.
[0112] 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.
[0113] 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.
[0114] 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.
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