Note: Descriptions are shown in the official language in which they were submitted.
CA 02848833 2015-11-04
ASCORBATE MODIFIED CROSSLINKED HYALURONIC ACID DERMAL FILLER
COMPOSITIONS THAT EXHIBIT REDUCED TYNDALL EFFECT
10
BACKGROUND
The present invention generally relates to dermal filler compositions, and
more
specifically relates to injectable dermal filler compositions that are
effective for
treatment of fine lines in skin.
Skin aging is a progressive phenomenon, occurs over time and can be affected
by
lifestyle factors, such as alcohol consumption, tobacco and sun exposure.
Aging
of the facial skin can be characterized by atrophy, slackening, and fattening.
Atrophy corresponds to a massive reduction of the thickness of skin tissue.
Slackening of the subcutaneous tissues leads to an excess of skin and ptosis
and
leads to the appearance of drooping cheeks and eye lids. Fattening refers to
an
increase in excess weight by swelling of the bottom of the face and neck.
These
changes are typically associated with dryness, loss of elasticity, and rough
texture.
Hyaluronic acid (HA), also known as hyaluronan, is a non-sulfated
glycosaminoglycan that is distributed widely throughout the human body in
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connective, epithelial, and neural tissues. Hyalurinic acid is abundant in the
different layers of the skin, where it has multiple functions such as, e.g.,
to ensure
good hydration, to assist in the organization of the extracellular matrix, to
act as a
filler material; and to participate in tissue repair mechanisms. However, with
age,
the quantity of hyaluronic acid, collagen, elastin, and other matrix polymers
present in the skin decreases. For example, repeated exposed to ultra violet
light,
e.g., from the sun, causes dermal cells to both decrease their production of
hyaluronan as well as increase the rate of its degradation. This loss of
materials
results in various skin conditions such as, e.g., wrinkling, hollowness, loss
of
moisture and other undesirable conditions that contribute to the appearance of
aging.
Injectable dermal fillers have been successfully used in treating the aging
skin.
The fillers can replace lost endogenous matrix polymers, or enhance/facilitate
the
function of existing matrix polymers, in order to treat these skin conditions.
Hyaluronic acid-based dermal fillers have become increasingly popular, as
hyaluronic acid is a substance naturally found throughout the human body.
These
fillers are generally well tolerated, nonpermanent, and a fairly low risk
treatment
for a wide variety of skin conditions.
Tyndall effect is an adverse event occurring in some patients administered
with
hyaluronic acid (HA)-based dermal fillers. Tyndall effect is characterized by
the
appearance of a blue discoloration at the skin site where a dermal filler had
been
injected, which represents visible hyaluronic acid seen through the
translucent
epidermis. Clinical reports suggest that filler administration technique and
skin
properties can influence the manifestation of this adverse event. Fillers with
high
stiffness and elasticity are successfully used to correct areas on the face
like
nasolabial folds, cheeks, and chin without any fear of facial discoloration,
as the
materials are injected in the mid and deep dermis regions. However, when these
filler materials are used to correct superficial, fine line wrinkles, for
example, tear
trough, glabellar lines periorbital lines, smile lines, or forehead, or
mistakenly
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applied too superficially in the upper regions of the dermis, a bluish
discoloration
of the skin is often observed. This phenomenon, which is thought to be the
result
of Tyndall effect, leaves a semi-permanent discoloration of the application
sites,
and sometimes disappears only after the administration of hyaluronidase to
degrade the filler material. Consequently, Tyndall effect is more common in
patients treated for superficial fine line wrinkles. Prolonged manifestation
of
Tyndall effect, typically for several months as long as the gel lasts in the
skin, is a
cause of major concern among patients.
HA- based dermal filler gels have been specifically formulated to treat "fine
line "
wrinkles found around the tear trough, forehead, periobital, glabellar lines,
etc.
Commercially available HA "fine line" gels include Juvederm Refine (G' ¨67 Pa;
GIG' ¨0.59, HA concentration 18 mg/ml), Belotero Soft (G' ¨28 Pa; G"/G' ¨1.1,
HA concentration 20 mg/ml), Emervel Touch' (G' ¨56 Pa; G"/G' ¨0.64, HA
concentration 20 mg/ml), Stylage S (G' ¨192 Pa; G"/G' ¨0.20, HA concentration
16 mg/ml), Teosyal First Lines (G' 59 Pa; G"/G' ¨0.53, HA concentration 20
mg/ml), Restylane Touch (G' ¨489 Pa; G"/G' ¨0.24, HA concentration 18 mg/ml).
Though these gels are formulated to have low elastic moduli, for example, by
lightly crosslinking the linear HA chains with a small amount of crosslinker
and/or
by reducing the final HA concentration of these gels, most of the commercially
available "fine line" gels still show Tyndall effect in some patients,
especially when
when injected superficially, for example, at a depth of less than about one
mm.
Collagen-based gels can be employed in the treatment of superficial wrinkles
and
does not appear to cause Tyndall effect. Collagen based gels are not highly
favored as they have relatively poor duration in the skin and require pre-
testing in
individuals. Radiesse (calcium hydroxylapatite) is a subdermal, injectable
implant, whose principal component is synthetic calcium hydroxylapatite, not
hyaluronic acid. Unlike hyaluronic acid-based dermal fillers, calcium
hydroxylapatite is not transparent, and thus avoids the complication of the
Tyndall
effect. However, if placed too superficially, this filler can be seen as a
white
Trademark*
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substance immediately beneath the skin. Furthermore, compared to hyaluronic
acid based fillers, Radiesse requires a larger needle for injection and is
not
typically recommended for use in the eye area.
It would be desirable to provide an injectable hyaluronic acid-based dermal
filler
that does not exhibit the bluish discoloration attributed to Tyndall effect,
even
when injected superficially.
SUMMARY
The present invention describes compositions and formulation methods for
preparing HA-based dermal fillers that can be administered in the upper dermis
without producing any bluish discoloration of the skin, or at least no
significant or
noticeable bluish discoloration. Further, many of the presently described
filler gels
of the invention have been found to last significantly longer in vivo than
current
commercially available gels. In some aspects of the invention, optically
transparent dermal fillers useful for enhancing the appearance of the skin are
provided which add volume and fullness, and reduce the appearance of even fine
line wrinkles without "tyndalling". The present compositions can be introduced
into
fine lines in the skin, even in regions of thin skin and rather superficially,
without
causing the negative blue discoloration associated with many conventional
optically transparent dermal fillers.
More specifically, in one aspect of the present invention, long lasting,
therapeutic
dermal filler compositions are provided which generally comprise a
biocompatible
polymer, for example, crosslinked hyaluronic acid component and an additive
combined with the hyaluronic acid component.
In one embodiment, the polymer is a polysaccharide, for example, hyaluronic
acid.
The hyaluronic acid includes a crosslinked component and may further include a
non-crosslinked component. The additive may comprise a vitamin, for example,
vitamin C, for example, a stabilized form of vitamin C, or a vitamin C
derivative,
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for example, L-ascorbic acid 2-glucoside (AA2G), ascobyl 3-aminopropyl
phosphate (Vitagen) or sodium ascorbyl phosphate (AA2P).
In one aspect of the invention, the additive is a vitamin derivative which is
covalently conjugated to the polymer by a suitable reaction process, for
example,
etherification, amidization or estherification.
In a broad aspect of the invention, a dermal filler composition is provided,
the
composition comprising
a hyaluronic acid component crosslinked with a
crosslinking component, and an additive other than the crosslinking component.
The hyaluronic acid component may be chemically conjugated to the additive.
Further, the composition exhibits reduced Tyndall effect when administered
into a
dermal region of a patient, relative to composition that is substantially
identical
except without the additive. The composition may further comprise other
additives, for example, an anesthetic agent, such as lidocaine. In one
embodiment
, the additive is a vitamin C derivative, for example, AA2G.
In another
embodiment, the additive is Vitagen.
In one embodiment, the hyaluronic acid component is chemically conjugated to
the additive with degree of conjugation being between about 3 mork and about
40
mol, for example, between about 3 mork and about 10 mor/o.
The composition may be substantially optically transparent. The compositions
generally have a G' value of between about 40 Pa and about 100 Pa, for
example, no greater than about 100 Pa and, for example, no less than about 40
Pa.
In another aspect of the invention, methods of treating fine lines in the skin
of a
patient are provided. In one embodiment, the method comprises the steps of
introducing, into skin of a patient, a composition comprising a mixture of a
hyaluronic acid component, a crosslinking component crosslinking the
hyaluronic
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acid, and an additive other than the crosslinking component, the
composition
being substantially optically transparent, and wherein the composition
exhibits
reduced Tyndall effect relative to composition that is substantially identical
except
without the additive.
In another aspect of the invention, methods of improving aesthetic appearance
of
a face are provided, the methods generally comprising the steps of
administering,
to a dermal region of a patient, a substantially optically transparent dermal
filler
composition that exhibits no or insignificant Tyndall effect. The composition
may
be made by the steps of providing hyaluronic acid, reacting a
crosslinking
agent with a vitamin C derivative, adding the reacted crosslinking agent and
vitamin C derivative to the hyaluronic acid to form a crosslinked hyaluronic
acid
composition including covalently conjugated vitamin C; and homogenizing
and neutralizing the crosslinked hyaluronic acid composition to obtain
an
injectable dermal filler composition. In
some embodiments, the vitamin C
derivative is AA2G. In other embodiments, the vitamin C derivative is Vitagen.
In yet another aspect of the invention, methods of reducing appearance of fine
lines in thin skin regions of a patient are provided, wherein the method
generally
comprises administering to the patient a dermal filler composition, at a depth
of no
greater than about 1 mm, a substantially optically transparent hyaluronic acid
based dermal filler composition including a vitamin C or a vitamin C
derivative. In
some embodiments, the composition is injected at a depth of a depth of no
greater
than about 0.8 mm, no greater than about 0.6 mm, or no greater than about 0.4
mm.
In yet another aspect of the invention, a dermal filler composition is
provided which
is substantially optically transparent, and generally comprises a hyaluronic
acid
component crosslinked with a crosslinking component, and a vitamin
C
derivative covalently conjugated to the hyaluronic acid component. In an
exemplary embodiment, the composition and having a G' value between about 40
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= ' '
Pa and about 100 Pa. Further, the composition may have a hyaluronic acid
concentration of between about 18 mg/g and about 30 mg/g. These compositions
may be especially useful and effective in treating fine lines or superficial
creases in
the skin, for example, even in very thin skin, for example, skin having a
thickness
of no greater than about 1 mm. In some embodiments, the compositions of the
invention last at least 3 months, at least 6 months or up to a year after
being
introduced into the skin.
In one aspect of the invention, the dermal filler compositions as described
herein are for
injection at a depth of no greater than about 1 mm. In a further embodiment
the dermal
filler compositions as described herein are for injection at' a depth of no
greater than
about 0.8 mm. In a further embodiment the dermal filler compositions as
described
herein are for injection at a depth of no greater than about 0.6 mm. In a
further
embodiment the dermal filler compositions as described herein are for
injection at a
depth of no greater than about 0.4 mm.
In a further embodiment, there is provided a dermal filler composition having
a
hyaluronic acid concentration of between about 12 mg/g and about 30 mg/g.
In a further embodiment, there is provided a composition having a HA
concentration of
about 25 mg/g.
In a further embodiment, there is provided a composition comprising hyaluronic
acid
which is at least 90% low molecular weight HA. In still a further embodiment
the
hyaluronic acid component is substantially entirely low molecular weight HA.
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, .
These and other aspects and advantages of the present invention may be more
readily understood and appreciated with referenced to the following drawings
and
detailed description.
BRIEF DESCRIPTION OF DRAWINGS
Figure 1 is a representation of the structure of [-ascorbic acid 2-glucoside
(AA2G)
Figure 2 is a representation of the structure of ascobyl 3-aminopropyl
phosphate
(Vitagen).
Figure 3 is a representation of the structure of sodium ascorbyl phosphate
(AA2P).
Figure 4 is a representation of the structure of 1,4-butanediol diglycidyl
ether
(BDDE).
Figure 5 is a representation of the structure of pentaerythritol glycidal
ether (Star-
PEG epoxide).
Figure 6 is a representation of the structure of pentaerythritol (3-
aminopropyl)
ether (Star-PEG amine).
Figure 7 is a Table showing conjugation degrees and G' values for various
dermal
filler compositions in accordance with the invention.
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Figure 8 is a Table showing conjugation degrees, HA concentration and G'
values
for HA-AA2G(BDDE) dermal filler compositions in accordance with the invention.
Figure 9 is a graphical representation of observed percent release of AsA from
a
solution of AA2G in PBS, in terms of time in minutes, for four different a-
glucosidase concentrations.
Figure 10 shows a representation of a release profile of free AsA from
conjugated
dermal fillers in accordance with the invention (sustained release) (AA2G
conversion in mol% versus reaction time).
Figure 11A and 11B show additional release data for various dermal fillers in
accordance with the invention.
Figure 12 shows images of skin after superficial injection of HA based dermal
filler
gels of the invention and some commercially available gels for fine line
application.
Figure 13 shows visual Tyndall scores of HA based dermal filler gels of the
invention and certain commercially available gels for fine line application.
Figure 14 shows (:)/0 of blue light remitted from skin of HA based dermal
filler gels
of the invention and some commercially available gels for fine line
application
Figure 15 shows overall (:)/0 of gel remaining after 1 week implantation of HA
based
dermal filler gels of the invention and some commercially available gels for
fine
line application.
Figure 16 shows overall (:)/0 of gel remaining at Week 0 , Week 12, Week 24
and
Week 40 of implanted HA based dermal filler gels of the invention and some
commercially available gels for fine line application.
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DETAILED DESCRIPTION
In one aspect of the invention, dermal filler compositions are provided, the
compositions generally comprising a biocompatible polymer, for example, a
polysaccharide such as a crosslinked hyaluronic acid, and a vitamin C
derivative
covalently conjugated to the polymer. The composition is provides sustained
release of the vitamin C for skin neocollagenesis as well as other therapeutic
or
cosmetic benefits. When introduced into the skin, for example intradermally,
the
composition reacts with endogeneous enzymes in the body, and over time,
bioactive vitamin C is generated in vivo, via enzymatic cleavages. As vitamin
C is
released from the composition over a period of weeks or months, its attendant
benefits are made available to the body.
The polymer may be selected from the group of polymers consisting of proteins,
peptides and polypeptides, polylysine, collagens, pro-collagens, elastins, and
laminins.
The polymer may be selected from the group of polymers consisting of synthetic
polymers with hydroxyl, amine, and carboxyl functional groups: poly(vinyl
alcohol),
polyethylene glycol, polyvinlyl amine, polyallylamine, deacetylated
polyacrylamide,
polyacrylic acid, and polymethacrylic acid. The polymer may be selected from
the
group of polymers consisting of dentric or branched polymers, including
dentric
polyols and dentric polyamines. The polymer may be selected from the group of
polymers consisting of solid surface with hydroxyl, amine, and carboxyl
functional
groups.
The polymer may be a polysaccharide, for example, selected from the group of
polysaccharides including starch and its derivatives; dextran and its
derivatives,
cellulose and its derivatives; chitin and chitosan and alginate and its
derivatives.
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,
In an exemplary embodiment of the invention, the polymer is glycosaminoglycan.
The hydrogel composition disclosed herein can further comprise two or more
different glycosaminoglycan polymers.
As used herein, the term
"glycosaminoglycan" is synonymous with "GAG" and "mucopolysaccharide" and
refers to long unbranched polysaccharides consisting of a repeating
disaccharide
units. The repeating unit consists of a hexose (six-carbon sugar) or a
hexuronic
acid, linked to a hexosamine (six-carbon sugar containing nitrogen) and
pharmaceutically acceptable salts thereof. Members of the GAG family vary in
the
type of hexosamine, hexose or hexuronic acid unit they contain, such as, e.g.,
glucuronic acid, iduronic acid, galactose, galactosamine, glucosamine) and may
also vary in the geometry of the glycosidic linkage. Any glycosaminoglycan
polymer is useful in the hydrogel compositions disclosed herein with the
proviso
that the glycosaminoglycan polymer improves a condition of the skin.
Non-
limiting examples of glycosaminoglycans include chondroitin sulfate, dermatan
sulfate, keratan sulfate, hyaluronan. Non-limiting examples of an acceptable
salt
of a glycosaminoglycans includes sodium salts, potassium salts, magnesium
salts,
calcium salts, and combinations thereof. Glycosaminoglycan and their resulting
polymers useful in the hydrogel compositions and methods disclosed herein are
described in, e.g., Piron and Tholin, Polysaccharide Crosslinking, Hydrogel
Preparation, Resulting Polysaccharides(s) and Hydrogel(s), uses Thereof, U.S.
Patent Publication 2003/0148995; Lebreton, Cross-Linking of Low and High
Molecular Weight Polysaccharides Preparation of Injectable Monophase
Hydrogels; Lebreton, Viscoelastic Solutions Containing Sodium Hyaluronate and
Hydroxypropyl Methyl Cellulose, Preparation and Uses, U.S. Patent Publication
2008/0089918; Lebreton, Hyaluronic Acid-Based Gels Including Lidocaine, U.S.
Patent Publication 2010/0028438; and Polysaccharides and Hydrogels thus
Obtained, U.S. Patent Publication 2006/0194758; and Di Napoli, Composition and
Method for Intradermal Soft Tissue Augmentation, International Patent
Publication
WO 2004/073759.
GAGs useful in the hydrogel compositions and methods disclosed herein
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PCT/US2012/055211
are commercially available, such as, e.g., hyaluronan-based dermal fillers
JUVEDERM , JUVEDERM 30, JUVEDERM Ultra, JUVEDERM Ultra Plus,
JUVEDERM Ultra XC, and JUVEDERM Ultra Plus XC (Allergan Inc, Irvine,
California). Table 1 lists representative GAGs.
Table 1. Examples of GAGs
Hexuronic Glycosidic
Name
acid/Hexose Hexosamine linkage Unique features
geometry
GaINAc or
Chondroitin GlcUA or GaINAc(4S) or -4GIcUA01-
Most prevalent GAG
sulfate GlcUA(2S) GaINAc(6S) or 3GaINAc/31-
GaINAc(4S,6S)
Distinguished from
chondroitin sulfate by
GaINAc or
GlcUA or the presence of iduronic
Dermatan GaINAc(4S) or -41doUA01-
1doUA or acid, although some
sulfate GaINAc(6S) or 3GaINAc01-
1doUA(2S) hexuronic acid
GaINAc(4S,6S)
monosaccharides may
be glucuronic acid.
Keratan sulfate type II
Keratan Gal or GIcNAc or -3Gal(6S)/31-
may
sulfate Gal(6S) GIcNAc(6S) be
fucosylated.
4GIcNAc(6S)/31-
GIcNAc or
Highest negative charge
GlcUA or GIcNS or
Heparin -4IdoUA(2S)a1- density of any known
IdoUA(2S) GIcNAc(6S) or 4GIcNS(6S)a1-
biological molecule
GIcNS(6S)
Highly similar in
structure to heparin,
GIcNAc or however heparan
GlcUA or
Heparan GIcNS or -4GIcUA/31- sulfates disaccharide
IdoUA or
sulfate GIcNAc(6S) or 4GIcNAca1- units are organized into
IdoUA(2S)
GIcNS(6S) distinct sulfated and
non-sulfated domains.
Hyaluronan GlcUA GIcNAc -4GIcUA01- The only GAG that is
3GIcNAc/31- exclusively non-sulfated
GlcUA = 6-D-glucuronic acid
GlcUA(2S) = 2-0-sulfo-6-D-glucuronic acid
IdoUA = a-L-iduronic acid
IdoUA(2S) = 2-0-sulfo-a-L-iduronic acid
Gal = 6-D-galactose
Gal(6S) = 6-0-sulfo-6-D-galactose
GaINAc = 6-D-N-acetylgalactosamine
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GaINAc(4S) = 6-D-N-acetylgalactosamine-4-0-sulfate
GaINAc(6S) = 6-D-N-acetylgalactosamine-6-0-sulfate
GaINAc(4S,6S) = 6-D-N-acetylgalactosamine-4-0, 6-0-sulfate
GIcNAc = a-D-N-acetylglucosamine
GIcNS = a-D-N-sulfoglucosamine
GIcNS(6S) = a-D-N-sulfoglucosamine-6-0-sulfate
Aspects of the present invention provide, in part, a hydrogel composition
comprising a chondroitin sulfate polymer. As used herein, the term
"chondroitin
sulfate polymer" refers to an unbranched, sulfated polymer of variable length
comprising disaccharides of two alternating monosaccharides of D-glucuronic
acid
(GIcA) and N-acetyl-D-galactosamine (GaINAc) and pharmaceutically acceptable
salts thereof. A chondroitin sulfate polymer may also include D-glucuronic
acid
residues that are epimerized into L-iduronic acid (IdoA), in which case the
resulting disaccharide is referred to as dermatan sulfate. A chondroitin
sulfate
polymer can have a chain of over 100 individual sugars, each of which can be
sulfated in variable positions and quantities. Chondroitin sulfate polymers
are an
important structural component of cartilage and provide much of its resistance
to
compression. Any chondroitin sulfate polymer is useful in the compositions
disclosed herein with the proviso that the chondroitin sulfate polymer
improves a
condition of the skin. Non-limiting examples of pharmaceutically acceptable
salts
of chondroitin sulfate include sodium chondroitin sulfate, potassium
chondroitin
sulfate, magnesium chondroitin sulfate, calcium chondroitin sulfate, and
combinations thereof.
Aspects of the present specification provide, in part, a hydrogel composition
comprising a keratan sulfate polymer. As used herein, the term "keratan
sulfate
polymer" refers to a polymer of variable length comprising disaccharide units,
which themselves include 6-D-galactose and N-acetyl-D-galactosamine (GaINAc)
and pharmaceutically acceptable salts thereof. Disaccharides within the
repeating
region of keratan sulfate may be fucosylated and N-Acetylneuraminic acid caps
the end of the chains. Any keratan sulfate polymer is useful in the
compositions
disclosed herein with the proviso that the keratan sulfate polymer improves a
condition of the skin. Non-limiting examples of pharmaceutically acceptable
salts
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of keratan sulfate include sodium keratan sulfate, potassium keratan sulfate,
magnesium keratan sulfate, calcium keratan sulfate, and combinations thereof.
Aspects of the present specification provide, in part, a hydrogel composition
comprising a hyaluronan polymer. As used herein, the term "hyaluronic acid
polymer" is synonymous with "HA polymer", "hyaluronic acid polymer", and
"hyaluronate polymer" refers to an anionic, non-sulfated glycosaminoglycan
polymer comprising disaccharide units, which themselves include D-glucuronic
acid and D-N-acetylglucosamine monomers, linked together via alternating [3 -1
,4
and [3 -1,3 glycosidic bonds and pharmaceutically acceptable salts thereof.
Hyaluronan polymers can be purified from animal and non-animal sources.
Polymers of hyaluronan can range in size from about 5,000 Da to about
20,000,000 Da. Any hyaluronan polymer is useful in the compositions disclosed
herein with the proviso that the hyaluronan improves a condition of the skin.
Non-
limiting examples of pharmaceutically acceptable salts of hyaluronan include
sodium hyaluronan, potassium hyaluronan, magnesium hyaluronan, calcium
hyaluronan, and combinations thereof.
Aspects of the present specification provide, in part, a hydrogel composition
comprising a crosslinked glycosaminoglycan polymer. As used herein, the term
"crosslinked" refers to the intermolecular bonds joining the individual
polymer
molecules, or monomer chains, into a more stable structure like a gel. As
such, a
crosslinked glycosaminoglycan polymer has at least one intermolecular bond
joining at least one individual polymer molecule to another one. The
crosslinking
of glycosaminoglycan polymers typically result in the formation of a hydrogel.
Such hydrogels have high viscosity and require considerable force to extrude
through a fine needle. Glycosaminoglycan polymers disclosed herein may be
crosslinked using dialdehydes and disulfides crosslinking agents including,
without
limitation, multifunctional PEG-based crosslinking agents, divinyl sulfones,
diglycidyl ethers, and bis-epoxides, biscarbodiimide. Non-limiting examples of
hyaluronan crosslinking agents include multifunctional PEG-based crosslinking
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,
agents like pentaerythritol tetraglycidyl ether (PETGE), divinyl sulfone
(DVS), 1,4-
butanedi01 diglycidyl ether (BDDE), 1,2-bis(2,3-epoxypropoxy)ethylene (EGDGE),
1,2,7,8-diepoxyoctane (DEO), (phenylenebis-(ethyl)-carbodiimide and 1,6
hexamethylenebis (ethylcarbodiimide), adipic
dihydrazide (ADH),
bis(sulfosuccinimidyl)suberate (BS), hexamethylenediamine (HMDA), 1-(2,3-
epoxypropy1)-2,3-epoxycyclohexane, lysine, lysine methylester, or combinations
thereof. Other useful cross-linking agents are disclosed in Stroumpoulis and
Tezel, Tunably Crosslinked Polysaccharide Compositions, U.S. Patent
Application
12/910,466, filed October 22, 2010.
Non-limiting examples of methods of crosslinking glycosaminoglycan
polymers are described in, e.g., Glycosaminoglycan polymers useful in the
compositions and methods disclosed herein are described in, e.g., Piron and
Thol in, Polysaccharide Crosslinking, Hydrogel
Preparation, Resulting
Polysaccharides(s) and Hydrogel(s), uses Thereof, U.S. Patent Publication
2003/0148995; Lebreton, Cross-Linking of Low and High Molecular Weight
Polysaccharides Preparation of Injectable Monophase Hydrogels; Lebreton,
Viscoelastic Solutions Containing Sodium Hyaluronate and Hydroxypropyl Methyl
Cellulose, Preparation and Uses, U.S. Patent Publication 2008/0089918;
Lebreton, Hyaluronic Acid-Based Gels Including Lidocaine, U.S. Patent
Publication 2010/0028438; and Polysaccharides and Hydrogels thus Obtained,
U.S. Patent Publication 2006/0194758; and Di Napoli, Composition and Method
for Intradermal Soft Tissue Augmentation, International Patent Publication WO
2004/073759.
Aspects of the present specification provide, in part, a hydrogel composition
comprising a crosslinked glycosaminoglycan polymer having a degree of
crosslinking. As used herein, the term "degree of crosslinking" refers to the
percentage of glycosaminoglycan polymer monomeric units, such as, e.g., the
disaccharide monomer units of hyaluronan that are bound to a cross-linking
agent.
The degree of crosslinking is expressed as the percent weight ratio of the
crosslinking agent to glycosaminoglycan. The degree of crosslinking in certain
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advantageous embodiment of the invention is between about 3% and about 12%,
for example, between about 5% and about 10%.
In an embodiment, a hydrogel composition comprises a crosslinked
glycosaminoglycan polymer, for example, crosslinked hyaluronic acid, wherein
the crosslinked glycosaminoglycan polymer is present in the composition at a
concentration of, for example, between about 18 mg/g and about 30 mg/g. In
some embodiments, the compositions have a total hyaluronic acid concentration
of about 24 mg/g or about 25 mg/g.
Aspects of the present specification provide, in part, a hydrogel composition
comprising hyaluronan polymers of low molecular weight, hyaluronan polymers of
high molecular weight, or hyaluronan polymers of both low and high molecular
weight. As used herein, the term "high molecular weight" when referring to
"hyaluronan" refers to hyaluronan polymers having a mean molecular weight of
1,000,000 Da or greater. Non-limiting examples of a high molecular weight
hyaluronan polymers include hyaluronan polymers about 1,500,000 Da, about
2,000,000 Da, about 2,500,000 Da, about 3,000,000 Da, about 3,500,000 Da,
about 4,000,000 Da, about 4,500,000 Da, and about 5,000,000 Da. As used
herein, the term "low molecular weight" when referring to "hyaluronan" refers
to
hyaluronan polymers having a mean molecular weight of less than 1,000,000 Da.
Non-limiting examples of a low molecular weight hyaluronan polymers include
hyaluronan polymers of about 200,000 Da, about 300,000 Da, about 400,000 Da,
about 500,000 Da, about 600,000 Da, about 700,000 Da, of about 800,000 Da,
and about 900,000 Da.
In an embodiment, a composition comprises crosslinked hyaluronan polymers of
low molecular weight. In aspects of this embodiment, a composition comprises
crosslinked hyaluronan polymers having a mean molecular weight of, e.g., about
100,000 Da, about 200,000 Da, about 300,000 Da, about 400,000 Da, about
500,000 Da, about 600,000 Da, about 700,000 Da, about 800,000 Da, or about
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900,000 Da. In yet other aspects of this embodiment, a composition comprises
crosslinked hyaluronan polymers having a mean molecular weight of, e.g., at
most
100,000 Da, at most 200,000 Da, at most 300,000 Da, at most 400,000 Da, at
most 500,000 Da, at most 600,000 Da, at most 700,000 Da, at most 800,000 Da,
at most 900,000 Da, or at most 950,000 Da. In still other aspects of this
embodiment, a composition comprises crosslinked hyaluronan polymers having a
mean molecular weight of, e.g., about 100,000 Da to about 500,000 Da, about
200,000 Da to about 500,000 Da, about 300,000 Da to about 500,000 Da, about
400,000 Da to about 500,000 Da, about 500,000 Da to about 950,000 Da, about
600,000 Da to about 950,000 Da, about 700,000 Da to about 950,000 Da, about
800,000 Da to about 950,000 Da, about 300,000 Da to about 600,000 Da, about
300,000 Da to about 700,000 Da, about 300,000 Da to about 800,000 Da, or
about 400,000 Da to about 700,000 Da.
In another embodiment, a composition comprises crosslinked hyaluronan
polymers of high molecular weight. In aspects of this embodiment, a
composition
comprises a crosslinked hyaluronan polymers having a mean molecular weight of,
e.g., about 1,000,000 Da, about 1,500,000 Da, about 2,000,000 Da, about
2,500,000 Da, about 3,000,000 Da, about 3,500,000 Da, about 4,000,000 Da,
about 4,500,000 Da, or about 5,000,000 Da. In yet other aspects of this
embodiment, a composition comprises a crosslinked hyaluronan polymers having
a mean molecular weight of, e.g., at least 1,000,000 Da, at least 1,500,000
Da, at
least 2,000,000 Da, at least 2,500,000 Da, at least 3,000,000 Da, at least
3,500,000 Da, at least 4,000,000 Da, at least 4,500,000 Da, or at least
5,000,000
Da. In still other aspects of this embodiment, a composition comprises a
crosslinked hyaluronan polymers having a mean molecular weight of, e.g., about
1,000,000 Da to about 5,000,000 Da, about 1,500,000 Da to about 5,000,000 Da,
about 2,000,000 Da to about 5,000,000 Da, about 2,500,000 Da to about
5,000,000 Da, about 2,000,000 Da to about 3,000,000 Da, about 2,500,000 Da to
about 3,000,000 Da.
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In yet another embodiment, a composition comprises a crosslinked hyaluronan
polymers where the crosslinked hyaluronan polymers comprise a combination of
both high molecular weight hyaluronan polymers and low molecular weight
hyaluronan polymers, in various ratios.
In aspects of this embodiment, a
composition comprises a crosslinked hyaluronan polymers where the crosslinked
hyaluronan polymers comprises a combination of both high molecular weight
hyaluronan polymers and low molecular weight hyaluronan polymers in a ratio of
about 20:1, about 15:1, about 10:1, about 5:1, about 1:1, about 1:5 about
1:10,
about 1:15, or about 1:20.
Aspects of the present specification provide, in part, a hydrogel composition
comprising an uncrosslinked glycosaminoglycan polymer. As used herein, the
term "uncrosslinked" refers to a lack of intermolecular bonds joining the
individual
glycosaminoglycan polymer molecules, or monomer chains. As such, an
uncrosslinked glycosaminoglycan polymer is not linked to any other
glycosaminoglycan polymer by an intermolecular bond.
In aspects of this
embodiment, a composition comprises an uncrosslinked chondroitin sulfate
polymer, an uncrosslinked dermatan sulfate polymer, an uncrosslinked keratan
sulfate polymer, an uncrosslinked heparan polymer, an uncrosslinked heparan
sulfate polymer, or an uncrosslinked hyaluronan polymer.
Uncrosslinked
glycosaminoglycan polymers are water soluble and generally remain fluid in
nature. As such, uncross-linked glycosaminoglycan polymers are often mixed
with
a glycosaminoglycan polymer-based hydrogel composition as a lubricant to
facilitate the extrusion process of the composition through a fine needle.
In an embodiment, a composition comprises an uncrosslinked glycosaminoglycan
polymer where the uncrosslinked glycosaminoglycan polymer is present at a
concentration of, e.g., about 2 mg/g, about 3 mg/g, about 4 mg/g, about 5
mg/g,
about 6 mg/g, about 7 mg/g, about 8 mg/g, about 9 mg/g, about 10 mg/g, about
11
mg/g, about 12 mg/g, about 13 mg/g, about 13.5 mg/g, about 14 mg/g, about 15
mg/g, about 16 mg/g, about 17 mg/g, about 18 mg/g, about 19 mg/g, about 20
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mg/g, about 40 mg/g, or about 60 mg/g. In other aspects of this embodiment, a
composition comprises an uncrosslinked glycosaminoglycan where the
uncrosslinked glycosaminoglycan is present at a concentration of, e.g., at
least 1
mg/g, at least 2 mg/g, at least 3 mg/g, at least 4 mg/g, at least 5 mg/g, at
least 10
mg/g, at least 15 mg/g, at least 20 mg/g, at least 25 mg/g at least 35 mg/g,
or at
least 40 mg/g. In yet other aspects of this embodiment, a composition
comprises
an uncrosslinked glycosaminoglycan where the uncrosslinked glycosaminoglycan
is present at a concentration of, e.g., at most 1 mg/g, at most 2 mg/g, at
most 3
mg/g, at most 4 mg/g, at most 5 mg/g, at most 10 mg/g, at most 15 mg/g, at
most
20 mg/g, or at most 25 mg/g. In still other aspects of this embodiment, a
composition comprises an uncrosslinked glycosaminoglycan where the
uncrosslinked glycosaminoglycan is present at a concentration of, e.g., about
1
mg/g to about 60 mg/g, about 10 mg/g to about 40 mg/g, about 7.5 mg/g to about
19.5 mg/g, about 8.5 mg/g to about 18.5 mg/g, about 9.5 mg/g to about 17.5
mg/g,
about 10.5 mg/g to about 16.5 mg/g, about 11.5 mg/g to about 15.5 mg/g, or
about
12.5 mg/g to about 14.5 mg/g.
Aspects of the present specification provide, in part, a hydrogel composition
that is
essentially free of a crosslinked glycosaminoglycan polymer. As used herein,
the
term "essentially free" (or "consisting essentially of") refers to a
composition where
only trace amounts of cross-linked matrix polymers can be detected. In an
aspect
of this embodiment, a composition comprises a chondroitin sulfate that is
essentially free of a crosslinked chondroitin sulfate polymer, a dermatan
sulfate
essentially free of a crosslinked dermatan sulfate polymer, a keratan sulfate
essentially free of a crosslinked keratan sulfate polymer, a heparan
essentially
free of a crosslinked heparan polymer, a heparan sulfate essentially free of a
crosslinked heparan sulfate polymer, or a hyaluronan sulfate essentially free
of a
crosslinked hyaluronan polymer.
Aspects of the present specification provide, in part, a hydrogel composition
that is
entirely free of a crosslinked glycosaminoglycan polymer. As used herein, the
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term "entirely free" refers to a composition that within the detection range
of the
instrument or process being used, crosslinked glycosaminoglycan polymers
cannot be detected or its presence cannot be confirmed. In an aspect of this
embodiment, a composition comprises a chondroitin sulfate that is entirely
free of
a crosslinked chondroitin sulfate polymer, a dermatan sulfate entirely free of
a
crosslinked dermatan sulfate polymer, a keratan sulfate entirely free of a
crosslinked keratan sulfate polymer, a heparan entirely free of a crosslinked
heparan polymer, a heparan sulfate entirely free of a crosslinked heparan
sulfate
polymer, or a hyaluronan sulfate entirely free of a crosslinked hyaluronan
polymer.
Aspects of the present specification provide, in part, a hydrogel composition
comprising a ratio of crosslinked glycosaminoglycan polymer and uncrosslinked
glycosaminoglycan polymer.
This ratio of crosslinked and uncrosslinked
glycosaminoglycan polymer is also known as the gel:fluid ratio. Any gel:fluid
ratio
is useful in making the compositions disclosed herein with the proviso that
such
ratio produces a composition disclosed herein that improves a skin condition
as
disclosed herein. Non-limiting examples of gel:fluid ratios in compositions of
the
present invention include 100:0, 98:2, 90:10, 75:25, 70:30, 60:40, 50:50,
40:60,
30:70, 25:75, 10:90; 2:98, and 0:100.
In aspects of this embodiment, a composition comprises a crosslinked
glycosaminoglycan polymer and an uncrosslinked glycosaminoglycan polymer
where the gel:fluid ratio is, e.g., about 0:100, about 1:99, about 2:98, about
3:97,
about 4:96, about 5:95, about 6:94, about 7:93, about 8:92, about 9:91, or
about
10:90. In other aspects of this embodiment, a composition comprises a
crosslinked glycosaminoglycan polymer and an uncrosslinked glycosaminoglycan
polymer where the gel:fluid ratio is, e.g., at most 1:99, at most 2:98, at
most 3:97,
at most 4:96, at most 5:95, at most 6:94, at most 7:93, at most 8:92, at most
9:91,
or at most 10:90. In yet other aspects of this embodiment, a composition
comprises a crosslinked glycosaminoglycan polymer and an uncrosslinked
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glycosaminoglycan polymer where the gel:fluid ratio is, e.g., about 0:100 to
about
3:97, about 0:100 to about 5:95, or about 0:100 to about 10:90.
In other aspects of this embodiment, a composition comprises a crosslinked
glycosaminoglycan polymer and an uncrosslinked glycosaminoglycan polymer
where the gel:fluid ratio is, e.g., about 15:85, about 20:80, about 25:75,
about
30:70, about 35:65, about 40:60, about 45:55, about 50:50, about 55:45, about
60:40, about 65:35, about 70:30, about 75:25, about 80:20, about 85:15, about
90:10, about 95:5, about 98:2, or about 100:0. In yet other aspects of this
embodiment, a composition comprises a crosslinked glycosaminoglycan polymer
and an uncrosslinked glycosaminoglycan polymer where the gel:fluid ratio is,
e.g.,
at most 15:85, at most 20:80, at most 25:75, at most 30:70, at most 35:65, at
most
40:60, at most 45:55, at most 50:50, at most 55:45, at most 60:40, at most
65:35,
at most 70:30, at most 75:25, at most 80:20, at most 85:15, at most 90:10, at
most
95:5, at most 98:2, or at most 100:0. In still other aspects of this
embodiment, a
composition comprises a crosslinked glycosaminoglycan polymer and an
uncrosslinked glycosaminoglycan polymer where the gel:fluid ratio is, e.g.,
about
10:90 to about 70:30, about 15:85 to about 70:30, about 10:90 to about 55:45,
about 80:20 to about 95:5, about 90:10 to about 100:0, about 75:25 to about
100:0, or about 60:40 to about 100:0.
A hydrogel composition disclosed herein may further comprise another agent or
combination of agents that provide a beneficial effect when the composition is
administered to an individual. Such beneficial agents include, without
limitation,
an antioxidant, an anti-itch agent, an anti-cellulite agent, an anti-scarring
agent, an
anti-inflammatory agent, an anesthetic agent, an anti-irritant agent, a
vasoconstrictor, a vasodilator, an anti-hemorrhagic agent like a hemostatic
agent
or anti-fibrinolytic agent, a desquamating agent, a tensioning agent, an anti-
acne
agent, a pigmentation agent, an anti-pigmentation agent, or a moisturizing
agent.
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For purposes of the present specification, unless otherwise stated, " /0" in a
formulation is defined as weight by weight (i.e., w/w) percentage.
Aspects of the present specification provide, in part, a hydrogel composition
disclosed herein that may optionally comprise an anesthetic agent. An
anesthetic
agent is preferably a local anesthetic agent, i.e., an anesthetic agent that
causes a
reversible local anesthesia and a loss of nociception, such as, e.g.,
aminoamide
local anesthetics and aminoester local anesthetics. The amount of an
anesthetic
agent included in a composition disclosed herein is an amount effective to
mitigate
pain experienced by an individual upon administration of the composition. As
such, the amount of an anesthetic agent included in a composition disclosed in
the
present specification is between about 0.1% to about 5% by weight of the total
composition. Non-limiting examples of anesthetic agents include
lidocaine,
ambucaine, amolanone, amylocaine, benoxinate, benzocaine, betoxycaine,
biphenamine, bupivacaine, butacaine, butamben, butanilicaine, butethamine,
butoxycaine, carticaine, chloroprocaine, cocaethylene, cocaine,
cyclomethycaine,
dibucaine, dimethysoquin, dimethocaine, diperodon, dycyclonine, ecgonidine,
ecgonine, ethyl chloride, etidocaine, beta-eucaine, euprocin, fenalcomine,
formocaine, hexylcaine, hydroxytetracaine, isobutyl p-aminobenzoate,
leucinocaine mesylate, levoxadrol, lidocaine, mepivacaine, meprylcaine,
metabutoxycaine, methyl chloride, myrtecaine, naepaine, octacaine, orthocaine,
oxethazaine, parethoxycaine, phenacaine, phenol, piperocaine, piridocaine,
polidocanol, pramoxine, prilocaine, procaine, propanocaine, proparacaine,
propipocaine, propoxycaine, psuedococaine, pyrrocaine, ropivacaine, salicyl
alcohol, tetracaine, tolycaine, trimecaine, zolamine, combinations thereof,
and
salts thereof. Non-limiting examples of aminoester local anesthetics include
procaine, chloroprocaine, cocaine, cyclomethycaine, cimethocaine (larocaine),
propoxycaine, procaine (novocaine), proparacaine, tetracaine (amethocaine).
Non-limiting examples of aminoamide local anesthetics include articaine,
bupivacaine, cinchocaine (dibucaine), etidocaine, levobupivacaine, lidocaine
(lignocaine), mepivacaine, piperocaine, prilocaine, ropivacaine, and
trimecaine. A
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composition disclosed herein may comprise a single anesthetic agent or a
plurality
of anesthetic agents. A non-limiting example of a combination local anesthetic
is
lidocaine/prilocaine (EMLA).
Thus in an embodiment, a composition disclosed herein comprises an anesthetic
agent and salts thereof. In aspects of this embodiment, a composition
disclosed
herein comprises an aminoamide local anesthetic and salts thereof or an
aminoester local anesthetic and salts thereof.
In other aspects of this
embodiment, a composition disclosed herein comprises procaine, chloroprocaine,
cocaine, cyclomethycaine, cimethocaine, propoxycaine, procaine, proparacaine,
tetracaine, or salts thereof, or any combination thereof. In yet other aspects
of this
embodiment, a composition disclosed herein comprises articaine, bupivacaine,
cinchocaine, etidocaine, levobupivacaine, lidocaine, mepivacaine, piperocaine,
prilocaine, ropivacaine, trimecaine, or salts thereof, or any combination
thereof. In
still other aspects of this embodiment, a composition disclosed herein
comprises a
lidocaine/prilocaine combination.
In other aspects of this embodiment, a composition disclosed herein comprises
an
anesthetic agent in an amount of, e.g., about 0.1%, about 0.2%, about 0.3%,
about 0.4%, about 0.5%, about 0.6%, about 0.7%, about 0.8% about 0.9%, about
1.0%, about 2.0%, about 3.0%, about 4.0%, about 5.0%, about 6.0%, about 7.0%,
about 8.0%, about 9.0%, or about 10% by weight of the total composition. In
yet
other aspects, a composition disclosed herein comprises an anesthetic agent in
an
amount of, e.g., at least 0.1%, at least 0.2%, at least 0.3%, at least 0.4%,
at least
0.5%, at least 0.6%, at least 0.7%, at least 0.8% at least 0.9%, at least
1.0%, at
least 2.0%, at least 3.0%, at least 4.0%, at least 5.0%, at least 6.0%, at
least
7.0%, at least 8.0%, at least 9.0%, or at least 10% by weight of the total
composition. In still other aspects, a composition disclosed herein comprises
an
anesthetic agent in an amount of, e.g., at most 0.1%, at most 0.2%, at most
0.3%,
at most 0.4%, at most 0.5%, at most 0.6%, at most 0.7%, at most 0.8% at most
0.9%, at most 1.0%, at most 2.0%, at most 3.0%, at most 4.0%, at most 5.0%, at
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most 6.0%, at most 7.0%, at most 8.0%, at most 9.0%, or at most 10% by weight
of the total composition. In further aspects, a composition disclosed herein
comprises an anesthetic agent in an amount of, e.g., about 0.1% to about 0.5%,
about 0.1% to about 1.0%, about 0.1% to about 2.0%, about 0.1% to about 3.0%,
about 0.1% to about 4.0%, about 0.1% to about 5.0%, about 0.2% to about 0.9%,
about 0.2% to about 1.0%, about 0.2% to about 2.0%, about 0.5% to about 1.0%,
or about 0.5% to about 2.0% by weight of the total composition.
In another embodiment, a composition disclosed herein does not comprise an
anesthetic agent.
In one aspect of the present invention, an injectable dermal filler is
provided which
comprises a polymer, for example, a glycosaminoglycan polymer, for example a
hyaluronic acid polymer, for example, a hyaluronic acid at least a portion of
which
is crosslinked, and an additive or beneficial agent combined with the polymer.
The beneficial agent combined with the polymer may comprise a vitamin, for
example, vitamin C. Non-limiting examples of suitable forms of vitamin C
include
ascorbic acid and sodium, potassium, and calcium salts of ascorbic acid, fat-
soluble esters of ascorbic acid with long-chain fatty acids (ascorbyl
palmitate or
ascorbyl stearate), magnesium ascorbyl phosphate (MAP), sodium ascorbyl
phosphate (SAP), and ascorbic acid 2-glucoside (AA2GTm), sodium ascorbyl
phosphate (AA2P), disodium ascorbyl sulfate, and ascobyl 3-aminopropyl
phosphate (Vitagen).
In an especially advantageous embodiment, the beneficial agent is covalently
conjugated to the polymer. For example, the beneficial agent may be a vitamin
C,
or a vitamin C derivative, which is covalently conjugated to the polymer and
is
present in the compositions in an amount between about 0.04% to about 5.0% by
weight of the total composition, for example, between about 0.1% to about 4.0%
by weight of the total composition, for example, between about 0.2% to about
2.0% by weight of the total composition. In one embodiment, the amount of
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vitamin C included in a composition disclosed herein is between about 0.3% to
about 1.2% by weight of the total composition.
Preferably, the vitamin C covalently conjugated to the polymer, includes at
least
one of ascorbic acid, L-ascorbic acid, L-ascorbic acid 2-sulfate (AA-2S) and L-
ascorbic acid 2-phosphate (AA-2P), ascorbic acid 2-0-glucoside (AA-2G), 6-0-
acy1-2-0-alpha-D-glucopyranosyl-L-ascorbic acids (6-Acyl-AA-2G), lascobyl 3-
aminopropyl phosphate, Ascorbyl palmitate), derivatives and combinations
thereof. A composition disclosed herein may comprise a single vitamin C agent
or a plurality of vitamin C agents.
In another embodiment of the invention, a dermal filler is provided wherein
the
hyaluronic acid is crosslinked with BDDE. In this embodiment, the degree of
conjugation may be between about 3 mol% and about 10 mol %, to about 15
mol% to about 40 mol%.
In some embodiments, the dermal fillers have a sustained bioavailability. For
example, dermal fillers are provided which, when introduced into the skin of a
human being, are effective to release ascorbic acid or other vitamin into the
human being for at least about 1 months and up to about 20 months or more.
Aspects of the present specification provide, in part, a hydrogel composition
disclosed herein that exhibits a complex modulus, an elastic modulus, a
viscous
modulus and/or a tan 6. The compositions as disclosed herein are viscoelastic
in
that the composition has an elastic component (solid-like such as, e.g.,
crosslinked glycosaminoglycan polymers) and a viscous component (liquid-like
such as, e.g., uncrosslinked glycosaminoglycan polymers or a carrier phase)
when
a force is applied (stress, deformation). The rheological attribute that
described
this property is the complex modulus (G*), which defines a composition's total
resistance to deformation. The complex modulus is a complex number with a real
and imaginary part: G*=g+iG". The absolute value of G* is Abs(G*) =
Sqrt(G12-1-G"2). The complex modulus can be defined as the sum of the elastic
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õ
modulus (G') and the viscous modulus (G").
Falcone, et al., Temporary
Polysaccharide Dermal Fillers: A Model for Persistence Based on Physical
Properties, Dermatol Surg. 35(8): 1238-1243 (2009); Tezel, supra, 2008;
Kablik,
supra, 2009; Beasley, supra, 2009.
Elastic modulus, or modulus of elasticity, refers to the ability of a hydrogel
material
to resists deformation, or, conversely, an object's tendency to be non-
permanently
deformed when a force is applied to it. Elastic modulus characterizes the
firmness
of a composition and is also known as the storage modulus because it describes
the storage of energy from the motion of the composition. The elastic modulus
describes the interaction between elasticity and strength (G' = stress/strain)
and,
as such, provides a quantitative measurement of a composition's hardness or
softness. The elastic modulus of an object is defined as the slope of its
stress-
strain curve in the elastic deformation region: A = stress/strain, where A is
the
elastic modulus in Pascal's; stress is the force causing the deformation
divided by
the area to which the force is applied; and strain is the ratio of the change
caused
by the stress to the original state of the object. Although depending on the
speed
at which the force is applied, a stiffer composition will have a higher
elastic
modulus and it will take a greater force to deform the material a given
distance,
such as, e.g., an injection. Specifying how stresses are to be measured,
including
directions, allows for many types of elastic moduli to be defined. The three
primary elastic moduli are tensile modulus, shear modulus, and bulk modulus.
Viscous modulus is also known as the loss modulus because it describes the
energy that is lost as viscous dissipation. Tan 6 is the ratio of the viscous
modulus
and the elastic modulus, tan 6 = G"/G'. Falcone, supra, 2009. For tan 6 values
disclosed in the present specification, a tan 6 is obtained from the dynamic
modulus at a frequency of 1 Hz. A lower tan 6 corresponds to a stiffer,
harder, or
more elastic composition.
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In another embodiment, a hydrogel composition disclosed herein exhibits an
elastic modulus. In aspects of this embodiment, a hydrogel composition
exhibits
an elastic modulus of, e.g., about 25 Pa, about 50 Pa, about 75 Pa, about 100
Pa,
about 125 Pa, about 150 Pa, about 175 Pa, about 200 Pa, about 250 Pa, about
300 Pa, about 350 Pa, about 400 Pa, about 450 Pa, about 500 Pa, about 550 Pa,
about 600 Pa, about 650 Pa, about 700 Pa, about 750 Pa, about 800 Pa, about
850 Pa, about 900 Pa, about 950 Pa, about 1,000 Pa, about 1,200 Pa, about
1,300 Pa, about 1,400 Pa, about 1,500 Pa, about 1,600 Pa, about 1700 Pa, about
1800 Pa, about 1900 Pa, about 2,000 Pa, about 2,100 Pa, about 2,200 Pa, about
2,300 Pa, about 2,400 Pa, or about 2,500 Pa. In other aspects of this
embodiment, a hydrogel composition exhibits an elastic modulus of, e.g., at
least
25 Pa, at least 50 Pa, at least 75 Pa, at least 100 Pa, at least 125 Pa, at
least 150
Pa, at least 175 Pa, at least 200 Pa, at least 250 Pa, at least 300 Pa, at
least 350
Pa, at least 400 Pa, at least 450 Pa, at least 500 Pa, at least 550 Pa, at
least 600
Pa, at least 650 Pa, at least 700 Pa, at least 750 Pa, at least 800 Pa, at
least 850
Pa, at least 900 Pa, at least 950 Pa, at least 1,000 Pa, at least 1,200 Pa, at
least
1,300 Pa, at least 1,400 Pa, at least 1,500 Pa, at least 1,600 Pa, at least
1700 Pa,
at least 1800 Pa, at least 1900 Pa, at least 2,000 Pa, at least 2,100 Pa, at
least
2,200 Pa, at least 2,300 Pa, at least 2,400 Pa, or at least 2,500 Pa. In yet
other
aspects of this embodiment, a hydrogel composition exhibits an elastic modulus
of, e.g., at most 25 Pa, at most 50 Pa, at most 75 Pa, at most 100 Pa, at most
125
Pa, at most 150 Pa, at most 175 Pa, at most 200 Pa, at most 250 Pa, at most
300
Pa, at most 350 Pa, at most 400 Pa, at most 450 Pa, at most 500 Pa, at most
550
Pa, at most 600 Pa, at most 650 Pa, at most 700 Pa, at most 750 Pa, at most
800
Pa, at most 850 Pa, at most 900 Pa, at most 950 Pa, at most 1,000 Pa, at most
1,200 Pa, at most 1,300 Pa, at most 1,400 Pa, at most 1,500 Pa, or at most
1,600
Pa. In still other aspects of this embodiment, a hydrogel composition exhibits
an
elastic modulus of, e.g., about 25 Pa to about 150 Pa, about 25 Pa to about
300
Pa, about 25 Pa to about 500 Pa, about 25 Pa to about 800 Pa, about 125 Pa to
about 300 Pa, about 125 Pa to about 500 Pa, about 125 Pa to about 800 Pa,
about 500 Pa to about 1,600 Pa, about 600 Pa to about 1,600 Pa, about 700 Pa
to
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about 1,600 Pa, about 800 Pa to about 1,600 Pa, about 900 Pa to about 1,600
Pa,
about 1,000 Pa to about 1,600 Pa, about 1,100 Pa to about 1,600 Pa, about
1,200
Pa to about 1,600 Pa, about 500 Pa to about 2,500 Pa, about 1,000 Pa to about
2,500 Pa, about 1,500 Pa to about 2,500 Pa, about 2,000 Pa to about 2,500 Pa,
about 1,300 Pa to about 1,600 Pa, about 1,400 Pa to about 1,700 Pa, about
1,500
Pa to about 1,800 Pa, about 1,600 Pa to about 1,900 Pa, about 1,700 Pa to
about
2,000 Pa, about 1,800 Pa to about 2,100 Pa, about 1,900 Pa to about 2,200 Pa,
about 2,000 Pa to about 2,300 Pa, about 2,100 Pa to about 2,400 Pa, or about
2,200 Pa to about 2,500 Pa.
In another embodiment, a hydrogel composition disclosed herein exhibits a
viscous modulus. In aspects of this embodiment, a hydrogel composition
exhibits
a viscous modulus of, e.g., about 10 Pa, about 20 Pa, about 30 Pa, about 40
Pa,
about 50 Pa, about 60 Pa, about 70 Pa, about 80 Pa, about 90 Pa, about 100 Pa,
about 150 Pa, about 200 Pa, about 250 Pa, about 300 Pa, about 350 Pa, about
400 Pa, about 450 Pa, about 500 Pa, about 550 Pa, about 600 Pa, about 650 Pa,
or about 700 Pa. In other aspects of this embodiment, a hydrogel composition
exhibits a viscous modulus of, e.g., at most 10 Pa, at most 20 Pa, at most 30
Pa,
at most 40 Pa, at most 50 Pa, at most 60 Pa, at most 70 Pa, at most 80 Pa, at
most 90 Pa, at most 100 Pa, at most 150 Pa, at most 200 Pa, at most 250 Pa, at
most 300 Pa, at most 350 Pa, at most 400 Pa, at most 450 Pa, at most 500 Pa,
at
most 550 Pa, at most 600 Pa, at most 650 Pa, or at most 700 Pa.. In yet other
aspects of this embodiment, a hydrogel composition exhibits a viscous modulus
of, e.g., about 10 Pa to about 30 Pa, about 10 Pa to about 50 Pa, about 10 Pa
to
about 100 Pa, about 10 Pa to about 150 Pa, about 70 Pa to about 100 Pa, about
50 Pa to about 350 Pa, about 150 Pa to about 450 Pa, about 250 Pa to about 550
Pa, about 350 Pa to about 700 Pa, about 50 Pa to about 150 Pa, about 100 Pa to
about 200 Pa, about 150 Pa to about 250 Pa, about 200 Pa to about 300 Pa,
about 250 Pa to about 350 Pa, about 300 Pa to about 400 Pa, about 350 Pa to
about 450 Pa, about 400 Pa to about 500 Pa, about 450 Pa to about 550 Pa,
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about 500 Pa to about 600 Pa, about 550 Pa to about 650 Pa, or about 600 Pa to
about 700 Pa.
In another embodiment, a hydrogel composition disclosed herein exhibits a tan
6.
In aspects of this embodiment, a hydrogel composition exhibits a tan 6 of,
e.g.,
about 0.1, about 0.2, about 0.3, about 0.4, about 0.5, about 0.6, about 0.7,
about
0.8, about 0.9, about 1.0, about 1.1, about 1.2, about 1.3, about 1.4, about
1.5,
about 1.6, about 1.7, about 1.8, about 1.9, about 2.0, about 2.1, about 2.2,
about
2.3, about 2.4, or about 2.5. In other aspects of this embodiment, a hydrogel
composition exhibits a tan 6 of, e.g., at most 0.1, at most 0.2, at most 0.3,
at most
0.4, at most 0.5, at most 0.6, at most 0.7, at most 0.8, at most 0.9, at most
1.0, at
most 1.1, at most 1.2, at most 1.3, at most 1.4, at most 1.5, at most 1.6, at
most
1.7, at most 1.8, at most 1.9, at most 2.0, at most 2.1, at most 2.2, at most
2.3, at
most 2.4, or at most 2.5. In yet other aspects of this embodiment, a hydrogel
composition exhibits a tan 6 of, e.g., about 0.1 to about 0.3, about 0.3 to
about 0.5,
about 0.5 to about 0.8, about 1.1 to about 1.4, about 1.4 to about 1.7, about
0.3 to
about 0.6, about 0.1 to about 0.5, about 0.5 to about 0.9, about 0.1 to about
0.6,
about 0.1 to about 1.0, about 0.5 to about 1.5, about 1.0 to about 2.0, or
about 1.5
to about 2.5.
Aspects of the present specification provide, in part, a hydrogel composition
disclosed herein having a transparency and/or translucency. Optical
transparency
is the physical property of allowing visible light to pass through a material,
whereas translucency (also called translucence or translucidity) only allows
light to
pass through diffusely. The opposite property is opacity. Transparent
materials
are clear, while translucent ones cannot be seen through clearly. The
hydrogels
disclosed herein are preferably optically transparent or at least translucent.
In an embodiment, a hydrogel composition disclosed herein is optically
translucent. In aspects of this embodiment, a hydrogel composition diffusely
transmits, e.g., about 75% of the light, about 80% of the light, about 85% of
the
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light, about 90% of the light, about 95% of the light, or about 100% of the
light. In
other aspects of this embodiment, a hydrogel composition diffusely transmits,
e.g.,
at least 75% of the light, at least 80% of the light, at least 85% of the
light, at least
90% of the light, or at least 95% of the light. In yet other aspects of this
embodiment, a hydrogel composition diffusely transmits, e.g., about 75% to
about
100% of the light, about 80% to about 100% of the light, about 85% to about
100%
of the light, about 90% to about 100% of the light, or about 95% to about 100%
of
the light. In an embodiment, a hydrogel composition disclosed herein is
optically
transparent and transmits 100% of visible light.
A hydrogel composition disclosed herein may be further processed by
pulverizing
the hydrogel into particles and optionally mixed with a carrier phase such as,
e.g.,
water or a saline solution to form an injectable or topical substance like a
solution,
oil, lotion, gel, ointment, cream, slurry, salve, or paste. As such, the
disclosed
hydrogel compositions may be monophasic or multiphasic compositions. A
hydrogel may be milled to a particle size from about 10 pm to about 1000 pm in
diameter, such as about 15 pm to about 30 pm, about 50 pm to about 75 pm,
about 100 pm to about 150 pm, about 200 pm to about 300 pm, about 450 pm to
about 550 pm, about 600 pm to about 700 pm, about 750 pm to about 850 pm, or
about 900 pm to about 1,000 pm.
Aspects of the present specification provide, in part, a composition disclosed
herein is injectable. As used herein, the term "injectable" refers to a
material
having the properties necessary to administer the composition into a skin
region of
an individual using an injection device with a fine needle. As used herein,
the term
"fine needle" refers to a needle that is 27 gauge or smaller. Injectability of
a
composition disclosed herein can be accomplished by sizing the hydrogel
particles
as discussed above.
In aspect of this embodiment, a hydrogel composition disclosed herein is
injectable through a fine needle. In other aspects of this embodiment, a
hydrogel
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composition disclosed herein is injectable through a needle of, e.g., about 27
gauge, about 30 gauge, or about 32 gauge. In yet other aspects of this
embodiment, a hydrogel composition disclosed herein is injectable through a
needle of, e.g., 22 gauge or smaller, 27 gauge or smaller, 30 gauge or
smaller, or
32 gauge or smaller. In still other aspects of this embodiment, a hydrogel
composition disclosed herein is injectable through a needle of, e.g., about 22
gauge to about 35 gauge, 22 gauge to about 34 gauge, 22 gauge to about 33
gauge, 22 gauge to about 32 gauge, about 22 gauge to about 27 gauge, or about
27 gauge to about 32 gauge.
In aspects of this embodiment, a hydrogel composition disclosed herein can be
injected with an extrusion force of about 60 N, about 55 N, about 50 N, about
45
N, about 40 N, about 35 N, about 30 N, about 25 N, about 20 N, or about 15 N
at
speeds of 100 mm/min. In other aspects of this embodiment, a hydrogel
composition disclosed herein can be injected through a 27 gauge needle with an
extrusion force of about 60 N or less, about 55 N or less, about 50 N or less,
about
45 N or less, about 40 N or less, about 35 N or less, about 30 N or less,
about 25
N or less, about 20 N or less, about 15 N or less, about 10 N or less, or
about 5 N
or less. In yet other aspects of this embodiment, a hydrogel composition
disclosed
herein can be injected through a 30 gauge needle with an extrusion force of
about
60 N or less, about 55 N or less, about 50 N or less, about 45 N or less,
about 40
N or less, about 35 N or less, about 30 N or less, about 25 N or less, about
20 N
or less, about 15 N or less, about 10 N or less, or about 5 N or less. In
still other
aspects of this embodiment, a hydrogel composition disclosed herein can be
injected through a 32 gauge needle with an extrusion force of about 60 N or
less,
about 55 N or less, about 50 N or less, about 45 N or less, about 40 N or
less,
about 35 N or less, about 30 N or less, about 25 N or less, about 20 N or
less,
about 15 N or less, about 10 N or less, or about 5 N or less.
Aspects of the present specification provide, in part, a hydrogel composition
disclosed herein that exhibits cohesivity. Cohesivity, also referred to as
cohesion
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cohesive attraction, cohesive force, or compression force is a physical
property of
a material, caused by the intermolecular attraction between like-molecules
within
the material that acts to unite the molecules. Cohesivity is expressed in
terms of
grams-force (gmf). Cohesiveness is affected by, among other factors, the
molecular weight ratio of the initial free glycosaminoglycan polymer, the
degree of
crosslinking of glycosaminoglycan polymers, the amount of residual free
glycosaminoglycan polymers following crosslinking, and the pH of the hydrogel
composition. A composition should be sufficiently cohesive as to remain
localized
to a site of administration.
Additionally, in certain applications, a sufficient
cohesiveness is important for a composition to retain its shape, and thus
functionality, in the event of mechanical load cycling.
As such, in one
embodiment, a hydrogel composition disclosed herein exhibits cohesivity, on
par
with water. In yet another embodiment, a hydrogel composition disclosed herein
exhibits sufficient cohesivity to remain localized to a site of
administration. In still
another embodiment, a hydrogel composition disclosed herein exhibits
sufficient
cohesivity to retain its shape. In a further embodiment, a hydrogel
composition
disclosed herein exhibits sufficient cohesivity to retain its shape and
functionality.
Aspects of the present specification provide, in part, a hydrogel composition
disclosed herein that exhibits a physiologically-acceptable osmolarity. As
used
herein, the term "osmolarity" refers to the concentration of osmotically
active
solutes in solution. As used herein, the term "a physiologically-acceptable
osmolarity" refers to an osmolarity in accord with, or characteristic of, the
normal
functioning of a living organism.
As such, administration of a hydrogel
composition as disclosed herein exhibits an osmolarity that has substantially
no
long term or permanent detrimental effect when administered to a mammal.
Osmolarity is expressed in terms of osmoles of osmotically active solute per
liter of
solvent (Osmol/L or Osm/L). Osmolarity is distinct from molarity because it
measures moles of osmotically active solute particles rather than moles of
solute.
The distinction arises because some compounds can dissociate in solution,
whereas others cannot. The osmolarity of a solution can be calculated from the
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following expression: Osmol/L = pi q, C,, where p is the osmotic
coefficient,
which accounts for the degree of non-ideality of the solution; q is the number
of
particles (e.g. ions) into which a molecule dissociates; and C is the molar
concentration of the solute; and i is the index representing the identity of a
particular solute. The osmolarity of a hydrogel composition disclosed herein
can
be measured using a conventional method that measures solutions.
In an embodiment, a hydrogel composition disclosed herein exhibits a
physiologically-acceptable osmolarity. As used herein, the term "osmolality"
refers
to the concentration of osmotically active solutes per kilo of solvent in the
body.
As used herein, the term "a physiologically-acceptable osmolality" refers to
an
osmolality in accord with, or characteristic of, the normal functioning of a
living
organism. As such, administration of a hydrogel composition disclosed herein
exhibits an osmolality that has substantially no long term or permanent
detrimental
effect when administered to a mammal. Osmolality is expressed in terms of
osmoles of osmotically active solute per kilogram of solvent (osmol/kg or
Osm/kg)
and is equal to the sum of the molalities of all the solutes present in that
solution.
The osmolality of a solution can be measured using an osmometer. The most
commonly used instrument in modern laboratories is a freezing point depression
osmometer. This instruments measure the change in freezing point that occurs
in
a solution with increasing osmolality (freezing point depression osmometer) or
the
change in vapor pressure that occurs in a solution with increasing osmolality
(vapor pressure depression osmometer).
In aspects of this embodiment, a hydrogel composition exhibits an osmolarity
of,
e.g., about 100 mOsm/L, about 150 mOsm/L, about 200 mOsm/L, about 250
mOsm/L, about 300 mOsm/L, about 350 mOsm/L, about 400 mOsm/L, about 450
mOsm/L, or about 500 mOsm/L. In other aspects of this embodiment, a hydrogel
composition exhibits an osmolarity of, e.g., at least 100 mOsm/L, at least 150
mOsm/L, at least 200 mOsm/L, at least 250 mOsm/L, at least 300 mOsm/L, at
least 350 mOsm/L, at least 400 mOsm/L, at least 450 mOsm/L, or at least 500
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mOsm/L. In yet other aspects of this embodiment, a hydrogel composition
exhibits an osmolarity of, e.g., at most 100 mOsm/L, at most 150 mOsm/L, at
most
200 mOsm/L, at most 250 mOsm/L, at most 300 mOsm/L, at most 350 mOsm/L,
at most 400 mOsm/L, at most 450 mOsm/L, or at most 500 mOsm/L. In still other
aspects of this embodiment, a hydrogel composition exhibits an osmolarity of,
e.g.,
about 100 mOsm/L to about 500 mOsm/L, about 200 mOsm/L to about 500
mOsm/L, about 200 mOsm/L to about 400 mOsm/L, about 300 mOsm/L to about
400 mOsm/L, about 270 mOsm/L to about 390 mOsm/L, about 225 mOsm/L to
about 350 mOsm/L, about 250 mOsm/L to about 325 mOsm/L, about 275 mOsm/L
to about 300 mOsm/L, or about 285 mOsm/L to about 290 mOsm/L.
Aspects of the present specification provide, in part, a hydrogel composition
disclosed herein that exhibits substantial stability. As used herein, the term
"stability" or "stable" when referring to a hydrogel composition disclosed
herein
refers to a composition that is not prone to degrading, decomposing, or
breaking
down to any substantial or significant degree while stored before
administration to
an individual. As used herein, the term "substantial heat stability",
"substantially
heat stable", "autoclave stable", or "steam sterilization stable" refers to a
hydrogel
composition disclosed herein that is substantially stable when subjected to a
heat
treatment as disclosed herein.
Stability of a hydrogel composition disclosed herein can be determined by
subjecting a hydrogel composition to a heat treatment, such as, e.g., steam
sterilization at normal pressure or under pressure (e.g., autoclaving).
Preferably
the heat treatment is carried out at a temperature of at least about 100 C
for
between about one minute and about 10 minutes. Substantial stability of a
hydrogel composition disclosed herein can be evaluated 1) by determining the
change in the extrusion force (AF) of a hydrogel composition disclosed herein
after
sterilization, where the change in extrusion force less 2N is indicative of a
substantially stable hydrogel composition as measured by (the extrusion force
of a
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hydrogel composition with the specified additives) minus (the extrusion force
of the
a hydrogel composition without the added additives); and/or 2) by determining
the
change in rheological properties of a hydrogel composition disclosed herein
after
sterilization, where the change in tan 6 1 Hz of less than 0.1 is indicative
of a
substantially stable hydrogel composition as measured by (tan 6 1 Hz of gel
formulation with additives) minus (tan 6 1 Hz of gel formulation without
additives).
As such, a substantially stable hydrogel composition disclosed herein retains
one
or more of the following characteristics after sterilization: homogeneousness,
extrusion force, cohesiveness, hyaluronan concentration, agent(s)
concentration,
osmolarity, pH, or other rheological characteristics desired by the hydrogel
before
the heat treatment.
In an embodiment, a hydrogel composition comprising a glycosaminoglycan
polymer and the at least one agent disclosed herein is processed using a heat
treatment that maintains the desired hydrogel properties disclosed herein. In
aspects of this embodiment, a hydrogel composition comprising a
glycosaminoglycan polymer and the at least one agent disclosed herein is
processed using a heat treatment of, e.g., about 100 C, about 10500 about 110
C, about 115 C, about 120 C, about 125 C, or about 130 C. In other aspects
of this embodiment, a hydrogel composition comprising a glycosaminoglycan
polymer and the at least one agent disclosed herein is processed using a heat
treatment of, e.g., at least 100 C, at least 105 C, at least 110 C, at
least 115 C,
at least 120 C, at least 125 C, or at least 130 C. In yet other aspects of
this
embodiment, a hydrogel composition comprising a glycosaminoglycan polymer
and the at least one agent disclosed herein is processed using a heat
treatment
of, e.g., about 100 C to about 120 C, about 100 C to about 125 C, about
100
C to about 13000 about 10000 to about 13500 about 11000 to about 12000
about 110 C to about 125 C, about 110 C to about 130 C, about 110 C to
about 135 C, about 120 C to about 125 C, about 120 C to about 130 C,
about
120 C to about 135 C, about 125 C to about 130 C, or about 125 C to about
135 C.
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Long term stability of a hydrogel composition disclosed herein can be
determined
by subjecting a hydrogel composition to a heat treatment, such as, e.g.,
storage in
an about 45 C environment for about 60 days. Long term stability of a
hydrogel
composition disclosed herein can be evaluated 1) by assessing the clarity and
color of a hydrogel composition after the 45 C heat treatment, with a clear
and
uncolored hydrogel composition being indicative of a substantially stable
hydrogel
composition; 2) by determining the change in the extrusion force (AF) of a
hydrogel composition disclosed herein after the 45 C heat treatment, where
the
change in extrusion force less 2N is indicative of a substantially stable
hydrogel
composition as measured by (the extrusion force of a hydrogel composition with
the specified additives before the 45 C heat treatment) minus (the extrusion
force
of the a hydrogel composition with the specified additives after the 45 C
heat
treatment); and/or 3) by determining the change in rheological properties of a
hydrogel composition disclosed herein after sterilization, where the change in
tan
EI 1 Hz of less than 0.1 is indicative of a substantially stable hydrogel
composition
as measured by (tan 0 1 Hz of gel formulation with the specified additives
before
the 45 C heat treatment) minus (tan 0 1 Hz of gel formulation with the
specified
additives after the 45 C heat treatment). As such, a long term stability of a
hydrogel composition disclosed herein is evaluated by retention of one or more
of
the following characteristics after the 45 C heat treatment: clarity
(transparency
and translucency), homogeneousness, and cohesiveness.
In aspects of this embodiment, a hydrogel composition is substantially stable
at
room temperature for, e.g., about 3 months, about 6 months, about 9 months,
about 12 months, about 15 months, about 18 months, about 21 months, about 24
months, about 27 months, about 30 months, about 33 months, or about 36
months. In other aspects of this embodiment, a hydrogel composition is
substantially stable at room temperature for, e.g., at least 3 months, at
least 6
months, at least 9 months, at least 12 months, at least 15 months, at least 18
months, at least 21 months, at least 24 months, at least 27 months, at least
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months, at least 33 months, or at least 36 months. In other aspects of this
embodiment, a hydrogel composition is substantially stable at room temperature
for, e.g., about 3 months to about 12 months, about 3 months to about 18
months,
about 3 months to about 24 months, about 3 months to about 30 months, about 3
months to about 36 months, about 6 months to about 12 months, about 6 months
to about 18 months, about 6 months to about 24 months, about 6 months to about
30 months, about 6 months to about 36 months, about 9 months to about 12
months, about 9 months to about 18 months, about 9 months to about 24 months,
about 9 months to about 30 months, about 9 months to about 36 months, about 12
months to about 18 months, about 12 months to about 24 months, about 12
months to about 30 months, about 12 months to about 36 months, about 18
months to about 24 months, about 18 months to about 30 months, or about 18
months to about 36 months.
The present compositions may optionally include, without limitation, other
pharmaceutically acceptable components, including, without limitation,
buffers,
preservatives, tonicity adjusters, salts, antioxidants, osmolality adjusting
agents,
emulsifying agents, wetting agents, and the like.
A pharmaceutically acceptable buffer is a buffer that can be used to prepare a
hydrogel composition disclosed herein, provided that the resulting preparation
is
pharmaceutically acceptable.
Non-limiting examples of pharmaceutically
acceptable buffers include acetate buffers, borate buffers, citrate buffers,
neutral
buffered salines, phosphate buffers, and phosphate buffered salines. Any
concentration of a pharmaceutically acceptable buffer can be useful in
formulating
a pharmaceutical composition disclosed herein, with the proviso that a
therapeutically effective amount of the active ingredient is recovered using
this
effective concentration of buffer. Non-limiting examples of concentrations of
physiologically-acceptable buffers occur within the range of about 0.1 mM to
about
900 mM. The pH of pharmaceutically acceptable buffers may be adjusted,
provided that the resulting preparation is pharmaceutically acceptable.
It is
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CA 02848833 2015-11-04
understood that acids or bases can be used to adjust the pH of a
pharmaceutical
composition as needed. Any buffered pH level can be useful in formulating a
pharmaceutical composition, with the proviso that a therapeutically effective
amount of the matrix polymer active ingredient is recovered using this
effective pH
level. Non-limiting examples of physiologically-acceptable pH occur within the
range of about pH 5.0 to about pH 8.5. For example, the pH of a hydrogel
composition disclosed herein can be about 5.0 to about 8.0, or about 6.5 to
about
7.5, about 7.0 to about 7.4, or about 7.1 to about 7.3.
Pharmaceutically acceptable preservatives include, without limitation, sodium
metabisulfite, sodium thiosulfate, acetylcysteine, butylated hydroxyanisole
and
butylated hydroxytoluene. Pharmaceutically acceptable preservatives include,
without limitation, benzalkonium chloride, chlorobutanol, thimerosal,
phenylmercuric acetate, phenylmercuric nitrate, a stabilized oxy chloro
composition, such as, e.g., PURITE (Allergan, Inc. Irvine, CA) and chelants,
such
as, e.g., DTPA or DTPA-bisamide, calcium DTPA, and CaNaDTPA-bisamide.
Pharmaceutically acceptable tonicity adjustors useful in a hydrogel
composition
disclosed herein include, without limitation, salts such as, e.g., sodium
chloride
and potassium chloride; and glycerin. The composition may be provided as a
salt
and can be formed with many acids, including but not limited to, hydrochloric,
sulfuric, acetic, lactic, tartaric, malic, succinic, etc. Salts tend to be
more soluble in
aqueous or other protonic solvents than are the corresponding free base forms.
It
is understood that these and other substances known in the art of pharmacology
can be included in a pharmaceutical composition disclosed herein. Other non-
limiting examples of pharmacologically acceptable components can be found in,
e.g., Ansel, supra, (1999); German), supra, (2000); Hardman, supra, (2001);
and
Rowe, supra, (2003) .
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Aspects of the present specification provide, in part, a method of treating a
soft
tissue condition of an individual by administering a hydrogel composition
disclosed
herein. As used herein, the term "treating," refers to reducing or eliminating
in an
individual a cosmetic or clinical symptom of a soft tissue condition
characterized
by a soft tissue imperfection, defect, disease, and/or disorder; or delaying
or
preventing in an individual the onset of a cosmetic or clinical symptom of a
condition characterized by a soft tissue imperfection, defect, disease, and/or
disorder. For example, the term "treating" can mean reducing a symptom of a
condition characterized by a soft tissue defect, disease, and/or disorder by,
e.g., at
least 20%, at least 30%, at least 40%, at least 50%, at least 60%, at least
70%, at
least 80%, at least 90% or at least 100%. The effectiveness of a hydrogel
composition disclosed herein in treating a condition characterized by a soft
tissue
defect, disease, and/or disorder can be determined by observing one or more
cosmetic, clinical symptoms, and/or physiological indicators associated with
the
condition. An improvement in a soft tissue defect, disease, and/or disorder
also
can be indicated by a reduced need for a concurrent therapy. Those of skill in
the
art will know the appropriate symptoms or indicators associated with specific
soft
tissue defect, disease, and/or disorder and will know how to determine if an
individual is a candidate for treatment with a compound or composition
disclosed
herein.
A hydrogel composition in accordance with the invention is administered to an
individual. An individual is typically a human being of any age, gender or
race.
Typically, any individual who is a candidate for a conventional procedure to
treat a
soft tissue condition is a candidate for a method disclosed herein. Although a
subject experiencing the signs of aging skin is an adult, subjects
experiencing
premature aging or other skin conditions suitable for treatment (for example,
a
scar) can also be treated with a hydrogel composition disclosed herein. In
addition, the presently disclosed hydrogel compositions and methods may apply
to
individuals seeking a small/moderate enlargement, shape change or contour
alteration of a body part or region, which may not be technically possible or
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aesthetically acceptable with existing soft tissue implant technology.
Pre-
operative evaluation typically includes routine history and physical
examination in
addition to thorough informed consent disclosing all relevant risks and
benefits of
the procedure.
The hydrogel composition and methods disclosed herein are useful in treating a
soft tissue condition. A soft tissue condition includes, without limitation, a
soft
tissue imperfection, defect, disease, and/or disorder. Non-limiting examples
of a
soft tissue condition include breast imperfection, defect, disease and/or
disorder,
such as, e.g., a breast augmentation, a breast reconstruction, mastopexy,
micromastia, thoracic hypoplasia, Poland's syndrome, defects due to implant
complications like capsular contraction and/or rupture; a facial imperfection,
defect, disease or disorder, such as, e.g., a facial augmentation, a facial
reconstruction, a mesotherapy, Parry-Romberg syndrome, lupus erythematosus
profundus, dermal divots, scars, sunken checks, thin lips, nasal imperfections
or
defects, retro-orbital imperfections or defects, a facial fold, line and/or
wrinkle like
a glabellar line, a nasolabial line, a perioral line, and/or a marionette
line, and/or
other contour deformities or imperfections of the face; a neck imperfection,
defect,
disease or disorder; a skin imperfection, defect, disease and/or disorder;
other soft
tissue imperfections, defects, diseases and/or disorders, such as, e.g., an
augmentation or a reconstruction of the upper arm, lower arm, hand, shoulder,
back, torso including abdomen, buttocks, upper leg, lower leg including
calves,
foot including plantar fat pad, eye, genitals, or other body part, region or
area, or a
disease or disorder affecting these body parts, regions or areas; urinary
incontinence, fecal incontinence, other forms of incontinence; and
gastroesophageal reflux disease (GERD). As used herein, the term
"mesotherapy" refers to a non-surgical cosmetic treatment technique of the
skin
involving intra-epidermal, intra-dermal, and/or subcutaneous injection of an
agent
administered as small multiple droplets into the epidermis, dermo-epidermal
junction, and/or the dermis.
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The amount of a hydrogel composition used with any of the methods as disclosed
herein will typically be determined based on the alteration and/or improvement
desired, the reduction and/or elimination of a soft tissue condition symptom
desired, the clinical and/or cosmetic effect desired by the individual and/or
physician, and the body part or region being treated. The effectiveness of
composition administration may be manifested by one or more of the following
clinical and/or cosmetic measures: altered and/or improved soft tissue shape,
altered and/or improved soft tissue size, altered and/or improved soft tissue
contour, altered and/or improved tissue function, tissue ingrowth support
and/or
new collagen deposition, sustained engraftment of composition, improved
patient
satisfaction and/or quality of life, and decreased use of implantable foreign
material.
Effectiveness of the compositions and methods in treating a facial soft tissue
may
be manifested by one or more of the following clinical and/or cosmetic
measures:
increased size, shape, and/or contour of facial feature like increased size,
shape,
and/or contour of lip, cheek or eye region; altered size, shape, and/or
contour of
facial feature like altered size, shape, and/or contour of lip, cheek or eye
region
shape; reduction or elimination of a wrinkle, fold or line in the skin;
resistance to a
wrinkle, fold or line in the skin; rehydration of the skin; increased
elasticity to the
skin; reduction or elimination of skin roughness; increased and/or improved
skin
tautness; reduction or elimination of stretch lines or marks; increased and/or
improved skin tone, shine, brightness and/or radiance; increased and/or
improved
skin color, reduction or elimination of skin paleness; sustained engraftment
of
composition; decreased side effects; improved patient satisfaction and/or
quality of
life.
As yet another example, for urinary incontinence procedures, effectiveness of
the
compositions and methods for sphincter support may be manifested by one or
more of the following clinical measures: decreased frequency of incontinence,
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sustained engraftment, improved patient satisfaction and/or quality of life,
and
decreased use of implantable foreign filler.
In aspects of this embodiment, the amount of a hydrogel composition
administered
is, e.g., about 0.01 g, about 0.05 g, about 0.1 g, about 0.5 g, about 1 g,
about 5 g,
about 10 g, about 20 g, about 30 g, about 40 g, about 50 g, about 60 g, about
70
g, about 80 g, about 90 g, about 100 g, about 150 g, or about 200 g. In other
aspects of this embodiment, the amount of a hydrogel composition administered
is, e.g., about 0.01 g to about 0.1 g, about 0.1 g to about 1 g, about 1 g to
about
10 g, about 10 g to about 100 g, or about 50 g to about 200 g. In yet other
aspects of this embodiment, the amount of a hydrogel composition administered
is, e.g., about 0.01 mL, about 0.05 mL, about 0.1 mL, about 0.5 mL, about 1
mL,
about 5 mL, about 10 mL, about 20 mL, about 30 mL, about 40 mL, about 50 mL,
about 60 mL, about 70 g, about 80 mL, about 90 mL, about 100 mL, about 150
mL, or about 200 mL. In other aspects of this embodiment, the amount of a
hydrogel composition administered is, e.g., about 0.01 mL to about 0.1 mL,
about
0.1 mL to about 1 mL, about 1 mL to about 10 mL, about 10 mL to about 100 mL,
or about 50 mL to about 200 mL.
The duration of treatment will typically be determined based on the cosmetic
and/or clinical effect desired by the individual and/or physician and the body
part
or region being treated. In aspects of this embodiment, administration of a
hydrogel composition disclosed herein can treat a soft tissue condition for,
e.g.,
about 6 months, about 7 months, about 8 months, about 9 months, about 10
months, about 11 months, about 12 months, about 13 months, about 14 months,
about 15 months, about 18 months, or about 24 months. In other aspects of this
embodiment, administration of a hydrogel composition disclosed herein can
treat a
soft tissue condition for, e.g., at least 6 months, at least 7 months, at
least 8
months, at least 9 months, at least 10 months, at least 11 months, at least 12
months, at least 13 months, at least 14 months, at least 15 months, at least
18
months, or at least 24 months. In yet aspects of this embodiment,
administration
of a hydrogel composition disclosed herein can treat a soft tissue condition
for,
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e.g., about 6 months to about 12 months, about 6 months to about 15 months,
about 6 months to about 18 months, about 6 months to about 21 months, about 6
months to about 24 months, about 9 months to about 12 months, about 9 months
to about 15 months, about 9 months to about 18 months, about 9 months to about
21 months, about 6 months to about 24 months, about 12 months to about 15
months, about 12 months to about 18 months, about 12 months to about 21
months, about 12 months to about 24 months, about 15 months to about 18
months, about 15 months to about 21 months, about 15 months to about 24
months, about 18 months to about 21 months, about 18 months to about 24
months, or about 21 months to about 24 months.
Aspects of the present specification provide, in part, administering a
hydrogel
composition disclosed herein. As used herein, the term "administering" means
any delivery mechanism that provides a composition disclosed herein to an
individual that potentially results in a clinically, therapeutically, or
experimentally
beneficial result. The actual delivery mechanism used to administer a
composition
to an individual can be determined by a person of ordinary skill in the art by
taking
into account factors, including, without limitation, the type of skin
condition, the
location of the skin condition, the cause of the skin condition, the severity
of the
skin condition, the degree of relief desired, the duration of relief desired,
the
particular composition used, the rate of excretion of the particular
composition
used, the pharmacodynamics of the particular composition used, the nature of
the
other compounds included in the particular composition used, the particular
route
of administration, the particular characteristics, history and risk factors of
the
individual, such as, e.g., age, weight, general health and the like, or any
combination thereof. In an aspect of this embodiment, a composition disclosed
herein is administered to a skin region of an individual by injection.
The route of administration of a hydrogel composition to an individual patient
will
typically be determined based on the cosmetic and/or clinical effect desired
by the
individual and/or physician and the body part or region being treated. A
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composition disclosed herein may be administered by any means known to
persons of ordinary skill in the art including, without limitation, syringe
with needle,
a pistol (for example, a hydropneumatic-compression pistol), catheter,
topically, or
by direct surgical implantation. The hydrogel composition disclosed herein can
be
administered into a skin region such as, e.g., a dermal region or a hypodermal
region. For example, a hydrogel composition disclosed herein can be injected
utilizing needles with a diameter of about 0.26 mm to about 0.4 mm and a
length
ranging from about 4 mm to about 14 mm. Alternately, the needles can be 21 to
32 G and have a length of about 4 mm to about 70 mm. Preferably, the needle is
a single-use needle. The needle can be combined with a syringe, catheter,
and/or
a pistol.
In addition, a composition disclosed herein can be administered once, or over
a
plurality of times. Ultimately, the timing used will follow quality care
standards. For
example, a hydrogel composition disclosed herein can be administered once or
over several sessions with the sessions spaced apart by a few days, or weeks.
For instance, an individual can be administered a hydrogel composition
disclosed
herein every 1, 2, 3, 4, 5, 6, or 7 days or every 1, 2, 3, or 4 weeks. The
administration a hydrogel composition disclosed herein to an individual can be
on
a monthly or bi-monthly basis or administered every 3, 6, 9, or 12 months.
Aspects of the present specification provide, in part, a dermal region. As
used
herein, the term "dermal region" refers to the region of skin comprising the
epidermal-dermal junction and the dermis including the superficial dermis
(papillary region) and the deep dermis (reticular region). The skin is
composed of
three primary layers: the epidermis, which provides waterproofing and serves
as a
barrier to infection; the dermis, which serves as a location for the
appendages of
skin; and the hypodermis (subcutaneous adipose layer). The epidermis contains
no blood vessels, and is nourished by diffusion from the dermis. The main type
of
cells which make up the epidermis are keratinocytes, melanocytes, Langerhans
cells and Merkels cells.
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The dermis is the layer of skin beneath the epidermis that consists of
connective
tissue and cushions the body from stress and strain. The dermis is tightly
connected to the epidermis by a basement membrane. It also harbors many
Mechanoreceptor/nerve endings that provide the sense of touch and heat. It
contains the hair follicles, sweat glands, sebaceous glands, apocrine glands,
lymphatic vessels and blood vessels. The blood vessels in the dermis provide
nourishment and waste removal from its own cells as well as from the Stratum
basale of the epidermis. The dermis is structurally divided into two areas: a
superficial area adjacent to the epidermis, called the papillary region, and a
deep
thicker area known as the reticular region.
The papillary region is composed of loose areolar connective tissue. It is
named
for its fingerlike projections called papillae that extend toward the
epidermis. The
papillae provide the dermis with a "bumpy" surface that interdigitates with
the
epidermis, strengthening the connection between the two layers of skin. The
reticular region lies deep in the papillary region and is usually much
thicker. It is
composed of dense irregular connective tissue, and receives its name from the
dense concentration of collagenous, elastic, and reticular fibers that weave
throughout it. These protein fibers give the dermis its properties of
strength,
extensibility, and elasticity. Also located within the reticular region are
the roots of
the hair, sebaceous glands, sweat glands, receptors, nails, and blood vessels.
Tattoo ink is held in the dermis. Stretch marks from pregnancy are also
located in
the dermis.
The hypodermis lies below the dermis. Its purpose is to attach the dermal
region
of the skin to underlying bone and muscle as well as supplying it with blood
vessels and nerves. It consists of loose connective tissue and elastin. The
main
cell types are fibroblasts, macrophages and adipocytes (the hypodermis
contains
50% of body fat). Fat serves as padding and insulation for the body.
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In an aspect of this embodiment, a hydrogel composition disclosed herein is
administered to a skin region of an individual by injection into a dermal
region or a
hypodermal region. In aspects of this embodiment, a hydrogel composition
disclosed herein is administered to a dermal region of an individual by
injection
into, e.g., an epidermal-dermal junction region, a papillary region, a
reticular
region, or any combination thereof.
Advantageously, some of the present compositions are especially useful and
effective in reducing appearance of fine lines, for example, in thin skin
regions, of
a patient. For example, methods are provided for fine line treatment
comprising
the steps of administering to the patient a dermal filler composition as
described
elsewhere herein, at a depth of no greater than about 1 mm.
Other aspects of the present specification disclose, in part, a method of
treating a
skin condition comprises the step of administering to an individual suffering
from a
skin condition a hydrogel composition disclosed herein, wherein the
administration
of the composition improves the skin condition, thereby treating the skin
condition.
In an aspect of this embodiment, a skin condition is a method of treating skin
dehydration comprises the step of administering to an individual suffering
from
skin dehydration a hydrogel composition disclosed herein, wherein the
administration of the composition rehydrates the skin, thereby treating skin
dehydration. In another aspect of this embodiment, a method of treating a lack
of
skin elasticity comprises the step of administering to an individual suffering
from a
lack of skin elasticity a hydrogel composition disclosed herein, wherein the
administration of the composition increases the elasticity of the skin,
thereby
treating a lack of skin elasticity. In yet another aspect of this embodiment,
a
method of treating skin roughness comprises the step of administering to an
individual suffering from skin roughness a hydrogel composition disclosed
herein,
wherein the administration of the composition decreases skin roughness,
thereby
treating skin roughness. In still another aspect of this embodiment, a method
of
treating a lack of skin tautness comprises the step of administering to an
individual
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suffering from a lack of skin tautness a hydrogel composition disclosed
herein,
wherein the administration of the composition makes the skin tauter, thereby
treating a lack of skin tautness.
In a further aspect of this embodiment, a method of treating a skin stretch
line or
mark comprises the step of administering to an individual suffering from a
skin
stretch line or mark a hydrogel composition disclosed herein, wherein the
administration of the composition reduces or eliminates the skin stretch line
or
mark, thereby treating a skin stretch line or mark. In another aspect of this
embodiment, a method of treating skin paleness comprises the step of
administering to an individual suffering from skin paleness a hydrogel
composition
disclosed herein, wherein the administration of the composition increases skin
tone or radiance, thereby treating skin paleness. In another aspect of this
embodiment, a method of treating skin wrinkles comprises the step of
administering to an individual suffering from skin wrinkles a hydrogel
composition
disclosed herein, wherein the administration of the composition reduces or
eliminates skin wrinkles, thereby treating skin wrinkles. In yet another
aspect of
this embodiment, a method of treating skin wrinkles comprises the step of
administering to an individual a hydrogel composition disclosed herein,
wherein
the administration of the composition makes the skin resistant to skin
wrinkles,
thereby treating skin wrinkles.
In some embodiments, the dermal fillers have a sustained bioavailability. For
example, dermal fillers are provided which, when introduced into the skin of a
human being, (for example, intradermally or subdermally into a human being for
the correction of soft tissue defects of voids in the face), release ascorbic
acid (or
other vitamin) into the human being for at least about 1 months and up to
about 20
months or more.
For example, to predict a sustained Vitamin C efficacy in coordinate with
filler
duration, an estimation on conjugated degree is made. This estimation was
based
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on the formulation of AA2G conjugation to HA via etherification. The
formulation is
stable under physiological conditions but start to release of Ascorbic acid
(AsA) by
a-glucosidase which is attached to the cell membrane. Release of AsA happens
at
the filler/cell interface due to the fact that a-glucosidase is attached to
cell
membrane. Further release of AsA from HA-AA2G will be accompanied by HA
degradation to make AA2G available to fibroblasts. The release of AsA is thus
depending on AA2G conjugation degree and duration of HA.
A gel with
conjugation degree of 5 mol% approximately could release active Vitamin C in a
period of at least up to 1 month, for example, between 3 ¨5 months; a gel with
10
mol (:)/0 conjugation degree could release active Vitamin C in a period up to
6-8
months; a gel with 15 mol% conjugation degree could release active Vitamin C
in
a period up to 10¨ months; 30 mol% up to one and half years.
Conjugation Total AsA Calculated number
degree (mol%) available*(mM) (months)**
3 2.13 2.8
5 3.55 3.1
1 7.10 6.3
15 10.65 9.4
17.75 15.7
21.13 18.8
* Based on parameters of Gels: volume, 0.1cc; concentration, 24 mg/ml. (0.1X
24 X 3% X1000)/(338*0.1)=2.13 (mM)
**Assumptions:
20 AsA is released at a constant rate.
Effective concentration of AsA is 0.05mM and maintains effective > 2 days 2.13
*2/ (0.05*30)=2.8 (months)
In an embodiment of the invention, a dermal filler is provided comprising
25 hyaluronic acid crosslinked with a Star-PEG epoxide and having a vitamin
C
derivative (for example, one of AA2G (Ascorbic acid 2-Glucoside), Vitagen (3-
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aminopropyl-L-ascorbyl phosphate) and SAP (sodium ascorbyl phosphate)
conjugated to the hyaluronic acid with a degree of conjugation of between
about 3
mol% and about 40 mol%.
Methods of making this dermal filler include reacting pentaerythritol glycidal
ether
(Star-PEG epoxide) with ascorbic acid 2-Glucoside (AA2G) at a ratio, reaction
temperature and reaction time suitable for achieving a composition containing
AA2G capped by 4-arm epoxides (AA2G-4 arm epoxides), unreacted 4-arm
epoxides and free AA2G. The 4 arm epoxide capped AA2G (AA2G-4 arm
epoxides) is conjugated to hyaluronic acid via the epoxyl group. The unreacted
4
arm epoxides serves as a crosslinker to crosslink hyaluronic acid and as a
conjugation agent to further conjugate AA2G.
In another embodiment of the invention, a dermal filler is provided comprising
hyaluronic acid crosslinked with BDDE and having a vitamin C derivative (for
example, one of AA2G (Ascorbic acid 2-Glucoside), Vitagen (3-aminopropyl-L-
ascorbyl phosphate) and SAP (sodium ascorbyl phosphate) conjugated to the
hyaluronic acid with a degree of conjugation of between about 3 mol% and about
10 mol%.
Methods of making this dermal filler include reacting BDDE with ascorbic acid
2-
Glucoside (AA2G) at a ratio, reaction temperature and reaction time suitable
for
achieve a composition containing AA2G capped by BDDE (AA2G-BDDE),
unreacted BDDE and free AA2G. The BDDE capped AA2G (AA2G-BDDE) is
conjugated to hyaluronic acid via the epoxyl group. The unreacted BDDE
serves as a crosslinker to crosslink hyaluronic acid and as a conjugation
agent to
further conjugate AA2G.
Figure 9 is a Table showing the effect of a-glucosidase concentration on AsA
release from AA2G ¨PBS solution. The conversion of AA2G to AsA depends on
the concentration of a-glycosidase. AA2G converted AsA almost completely in 15
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minutes when a-glycosidase concentration is 6.3 unit per gram gel. When a-
glycosidase concentration is 4.7 units per gram gel, It took 30 minutes to
completely convert AA2G to AsA. Further decease a-glycosidase concentration
resulted in slow conversion of AA2G to AsA.
Figure 10 shows a representation of a release profile of free AsA from
conjugated
dermal fillers in accordance with the invention (sustained release) (AA2G
conversion in mol% versus reaction time). AA2G completely converted to AsA in
AA2G/HA mix in 40 minutes. AA2H/HA conjugates showed a time dependence of
AA2G conversion to AsA.
Figure 11A and 11B show additional release data for various dermal fillers in
accordance with the invention. More specifically, conversion of AA2G to AsA in
HA-AA2G gels is dependent on a-glycosidase concentration. High a-glycosidase
concentration resulted in a fast conversion of AA2G to AsA. For a given a-
glycosidase concentration, different formulations showed different profiles of
AA2G to AsA.
In one aspect of the invention, dermal fillers are provided which are
especially
effective in treating and eliminating the appearance of fine lines, for
example,
relatively superficial, creases in the skin, for example, but not limited to,
fine lines
near the eyes, the tear trough region, forehead, periorbital, glabellar lines,
etc.
The appearance of a blue discoloration at the skin site where a dermal filler
had
been injected, (Tyndall effect) is a significant adverse event experienced by
some
dermal filler patients. Tyndall effect is more common in patients treated for
superficial fine line wrinkles. Embodiments of the present invention have been
developed which provide long lasting, translucent fillers which can be
injected
superficially to treat fine lines and wrinkles, even in regions of relatively
thin skin,
without any resulting blue discoloration from Tyndall effect. Fine
lines or
superficial wrinkles are generally understood to be those wrinkles or creases
in
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skin that are typically found in regions of the face( forehead, lateral
canthus,
vermillion border/perioral lines) where the skin is thinnest, that is, the
skin has a
dermis thickness of less than 1 mm. On the forehead the average dermal
thickness is about 0.95 mm for normal skin and about 0.81 mm for wrinkled
skin.
Dermis around the lateral canthus is even thinner (e.g. about 0.61 mm for
normal
skin and about 0.41 mm for wrinkled skin). The average outer diameter of a 30
or
32 gauge needle (needles that are typically used for fine line gel
application) is
about 0.30 and about 0.24 mm.
The present invention provides a dermal filler composition such as described
elsewhere herein, which does not result in Tyndall effect.
For example,
compositions of the invention comprise a hyaluronic acid component crosslinked
with a crosslinking component,
an additive other than the crosslinking
component;. the composition exhibiting reduced Tyndall effect when
administered
into a dermal region of a patient, relative to composition that is
substantially
identical except without the additive. The composition may be substantially
optically transparent.
In one embodiment, the additive is a vitamin C derivative, for example, AA2G
which may be chemically conjugated to the hyaluronic acid as described
elsewhere herein.
In some embodiments, the crosslinking component is BDDE and the degree of
conjugation is between about 3 mork and about 10 mor/o, or up to 15 mork or
greater. In some embodiments, the composition further comprises an anesthetic
agent, for example, lidocaine in an amount suitable for providing comfort to
the
patient upon injection.
Methods of treating fine lines in the skin of a patient are also provided. The
methods generally comprise the steps of
introducing into skin of a patient, a
composition such as described herein. For example the compositions comprise
a mixture of a hyaluronic acid component, a crosslinking component
crosslinking
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the hyaluronic acid, and an additive other than the crosslinking component,
the
composition being substantially optically transparent; and wherein the dermal
filler
composition exhibits reduced Tyndall effect relative to composition that is
substantially identical except without the additive.
In some embodiments of the invention, the composition comprises a hyaluronic
acid component crosslinked with di - or multiamine crosslinker using EDC
chemistry. For example, the crosslinker may be HMDA.
In certain embodiments of the invention in which the crosslinker is HMDA, the
composition has a G' of up to about 70 Pa, G"/G' between about 0.65 and about
0.75, extrusion force of about 24 N or less, and a final HA concentration of
between about 24 mg/g and about 25 mg/g.
In certain embodiments of the invention in which the additive is HA-AA2G
conjugate or HA-Vitagen conjugate, the conjugation degree is between about 3
mol% and about 10 mol%, or up to about 15 mol%, or up to about 40 mol%.
These compositions may have a G' from at least about 30 Pa, more preferably at
least about 40 Pa, to about 100 Pa, G"/G' between about 0.30 and about 0.50,
extrusion force of about 27 N or less and a final HA concentration of between
about 24 mg/g and about 25 mg/g.
For purposes of the present disclosure, "degree of conjugation" as used herein
is
defined as molar percentage of conjugant, e.g., AA2G, to the repeating unit of
hyaluronic acid (e.g., HA dimer). Thus, 10 mol% conjugation degree means every
100 HA repeat units contain 10 conjugated AA2G. Degree of conjugation can be
calculated using the method illustrated in Example 2 below, or other methods
known to those of skill in the art.
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EXAMPLES
Example 1: AA2G conjugation to crosslinked HA Gels
using BODE as a crosslinker
400.6 mg of low molecular weight hyaluronic acid (LMW HA) was hydrated in 1802
mg of 1 wt% NaOH in a syringe for ¨30min. 800.7 mg of AA2G was put in a vial,
followed by 713.7 mg of BDDE and 1416.8 mg of 10% NaOH. The above solution
(pH >12) was allowed to react in a 50 C water bath for ¨20min, before adding
to
the hydrated HA. After the addition, the mixture was mixed ¨20 times by
passing
back and forth between 2 syringes. The mixed paste was put in a vial and in
the
50 C water bath for ¨2.5 hours. 223.5 mg of 12M HCI was added to 9.05 g PBS,
pH7.4. After ¨2.5 hours, the HA-AA2G gel was formed. The gel was cut into
pieces, and the HCI-PBS solution was added to it. The gel was allowed to
neutralize and swell overnight on an orbital shaker. The gel was sized through
a
¨60 pm screen and mixed ¨20 times by passing back and forth between 2
syringes. The gel was put in a 15,000 MWCO RC dialysis bag and dialyzed in
PBS, pH7.4 buffer. The dialysis went on for ¨185 hours, with frequent change
of
PBS buffer. After the dialysis, the gel was put in a syringe and stored in a 4
C
refrigerator.
Example 2: Determination of AA2G conjugations
The weight of gel as described in Example 1 was noted right before dialysis,
and
after dialysis. The assumption was made that the gel was ¨1g/mL after
dialysis.
The dialysis was stopped at the point where no notable AA2G was coming out per
> 8 hours in 1L of PBS. The AA2G was measured at 260nm using UV/Vis
spectrophotometer (Nanodrop 20000, ThermoScientific). The calibration curve of
AA2G was calculated using different concentration of AA2G in 2% HA (A@260nm
= 1.4838 [AA2G(mM)]).
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The weight of HA after dialysis: the starting weight of HA x (actual weight
before
dialysis / theoretical weight)
The mmol of AA2G after dialysis: put the absorption @ 260nm after dialysis in
the
equation (A@260nm = 1.4838 [AA2G(mM)]).
The conjugation @ of AA2G: (mmol of AA2G/mmol of HA)x100%
The AA2G conjugation degree in the gel as described in Example 1 is 14.7 mol%.
Example 3: Determination of gel rheoloqical properties
An oscillatory parallel plate rheometer (Anton Paar, Physica MCR 301) was used
to measure the properties of the gel obtained in Example 1. The diameter of
plate
used was 25 mm. The gap between the plates was set at 1 mm. For each
measurement, a frequency sweep at a constant strain was run first, before the
strain sweep at a fixed frequency. The G' (storage modulus) was obtained from
the strain sweep curve at 1% strain. The value is 1450 Pa for the gel.
Example 4: AA2G conjugation to crosslinked HA Gels using BDDE as a
crosslinker, with tunable conjugation degree and gel rheoloqical properties
The procedure was similar to that as described in Example 1. Conjugation
degree
is modified by tuning crosslinker to HA and AA2G mol ratios. Gel properties
were
measured as described in Example 3. Details are as follows:
400.8 mg of LMW HA was hydrated in 1752.1 mg of 1% NaOH in a syringe for
¨30min. 800.3 mg of AA2G was put in a vial, followed by 354.1 mg of BDDE and
1402.0 mg of 10% NaOH. The above solution (pH >12) was allowed to react in a
50 C water bath for ¨20min, before adding to the hydrated HA. After the
addition,
the mixture was mixed ¨20 times by passing back and forth between 2 syringes.
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The mixed paste was put in a vial and in the 50 C water bath for ¨2.5 hours.
140.9 mg of 12M HCI was added to 9.0053 g PBS, pH7.4. After ¨2.5 hours, the
HA-AA2G gel was formed. The gel was cut into pieces, and the HCI-PBS solution
was added to it. The gel was allowed to neutralize and swell overnight on an
orbital shaker. The gel was sized through a ¨60 pm screen and mixed ¨20 times
by passing back and forth between 2 syringes. The gel was put in a 15,000
MWCO RC dialysis bag and dialyzed in PBS, pH7.4 buffer. The dialysis went on
for ¨164.5 hours, with frequent change of PBS buffer. After the dialysis, the
gel
was put in a syringe and stored in a 4 C refrigerator. The conjugation degree
is
13%. Gel storage modulus (G') is 803 Pa.
Example 5: AA2G conjugation to crosslinked HA Gels using BODE as a
crosslinker, conjugation degree is 5.3 %, G' is ¨ 300 Pa.
400.3 mg of LMW HA was hydrated in 3002.0 mg of 1% NaOH in a syringe for
¨30min. 800.5 mg of AA2G was put in a vial, followed by 264.3 mg of BDDE and
1100.0 mg of 10% NaOH. The above solution (pH >12) was allowed to react in a
50 C water bath for ¨20min, before adding to the hydrated HA. After the
addition,
the mixture was mixed ¨20 times by passing back and forth between 2 syringes.
The mixed paste was put in a vial and in the 50 C water bath for ¨2.5 hours.
104.2 mg of 12M HCI was added to 8.5128 g PBS, pH7.4. After ¨2.5 hours, the
HA-AA2G gel was formed, and the HCI-PBS solution was added to it. The gel was
allowed to neutralize and swell over the weekend (-55 hours) on an orbital
shaker.
The gel was sized through a ¨60 pm screen and mixed ¨20 times by passing back
and forth between 2 syringes. The gel was put in a 15,000 MWCO RC dialysis bag
and dialyzed in PBS, pH7.4 buffer. The dialysis went on for ¨114 hours, with
frequent change of PBS buffer. After the dialysis, the gel was put in a
syringe and
stored in a 4 C refrigerator. The conjugation degree and gel rheological
properties
are measured in a procedure as described in Example 2 and 3. The conjugation
degree is 5.3%. Gel storage modulus is ¨ 300 Pa.
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Example 6: AA2G conjugation to crosslinked HA Gels using star-PEG
epoxide as a crosslinker, conjugation degree is 29.4 %, G' is ¨ 235 Pa.
200.4 mg of LMW HA was hydrated in 2000 mg of 1% NaOH in a syringe for
¨30min. 400 mg of AA2G was put in a vial, followed by 312.7 mg of star-PEG
epoxide and 1026.5 mg of 10% NaOH. The above solution was allowed to react in
a 50 C water bath for ¨20min, before adding to the hydrated HA. After the
addition, the mixture was mixed ¨20 times by passing back and forth between 2
syringes. The mixed paste was put in a vial and in the 50 C water bath for
¨2.5
hours. 187.4 mg of 12M HCI was added to 3.034 g PBS, pH7.4. After ¨2.5 hours,
the HA-AA2G gel was formed, and the HCI-PBS solution was added to it. The gel
was allowed to neutralize and swell over the weekend (-68 hours) on an orbital
shaker. The gel was sized through a ¨60 pm screen and mixed ¨20 times by
passing back and forth between 2 syringes. The gel was put in a 15,000 MWCO
RC dialysis bag and dialyzed in PBS, pH 7.4 buffer. The dialysis went on for
¨95
hours, with frequent change of PBS buffer. After the dialysis, the gel was put
in a
syringe and stored in a 4 C refrigerator. The conjugation degree and gel
rheological properties are measured in a procedure as described in Examples 2
and 3. The conjugation degree is 29.4%. Gel storage modulus is ¨ 235 Pa.
Example 7: AA2G conjugation to crosslinked HA Gels using star-PEG
epoxide as a crosslinker, conjugation degree is 27.8 %, G' is ¨ 363 Pa.
200.3 mg of LMW HA was hydrated in 2000 mg of 1% NaOH in a syringe for
¨30min. 400.2 mg of AA2G was put in a vial, followed by 313.4 mg of star-PEG
epoxide and 1022.6 mg of 10% NaOH. The above solution was added to the
hydrated HA. After the addition, the mixture was mixed ¨20 times by passing
back
and forth between 2 syringes. The mixed paste was put in a vial and in the 50
C
water bath for ¨2.5 hours. 196.5 mg of 12M HCI was added to 3.016 g PBS,
pH7.4. After ¨2.5 hours, the HA-AA2G gel was formed, and the HCI-PBS solution
was added to it. The gel was allowed to neutralize and swell overnight (-24
hours)
on an orbital shaker. The gel was sized through a ¨60 pm screen and mixed ¨20
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times by passing back and forth between 2 syringes. The gel was put in a
15,000
MWCO RC dialysis bag and dialyzed in PBS, pH7.4 buffer. The dialysis went on
for ¨98.5 hours, with frequent change of PBS buffer. After the dialysis, the
gel was
put in a syringe and stored in a 4 C refrigerator. The conjugation degree and
gel
rheological properties are measured in a procedure as described in Examples 2
and 3. The conjugation degree is 27.8%. Gel storage modulus is ¨ 363 Pa.
Example 8: AA2G conjugation to crosslinked HMW HA Gels using BDDE as
a crosslinker, conjugation degree is about 10 mol %, G' is about 240 Pa.
400.3 mg of HMW HA was hydrated in 2501.3 mg of 4 wt% NaOH in a syringe for
¨30min. 1200 mg of AA2G was put in a vial, followed by 304.7 mg of BDDE and
1178.6 mg of 16 wt% NaOH. The above solution (pH >12) was allowed to react in
a 50 C water bath for ¨20min and transferred to a 20 cc syringe, before
adding to
the hydrated HA. After the addition, the mixture was mixed ¨20 times by
passing
back and forth between 2 syringes. The mixed paste was put in a 20 cc vial and
in
the 50 C water bath for ¨2.5 hours. After ¨2.5 hours, the HA-AA2G gel was
formed. Then 226.6 mg of 12M HCI was added to 8492.2 mg 10X PBS, pH7.4 to
get HCI-PBS solution and the HCI-PBS solution was added to neutralize and
swell
the gel. The gel was allowed to neutralize and swell over 48 hrs on an orbital
shaker. The gel was sized through a ¨60 pm screen and mixed ¨20 times by
passing back and forth between 2 syringes. The gel was put in a 20,000 MWCO
CE dialysis bag and dialyzed in PBS, pH7.4 buffer. The dialysis went on for
¨114
hours, with frequent change of PBS buffer. After the dialysis, the gel was put
in a
syringe and stored in a 4 C refrigerator. The conjugation degree and gel
rheological properties are measured in a procedure as described in Examples, 2
and 3. The conjugation degree is 10 mol%. Gel storage modulus is about 240 Pa.
Example 9: Vitaqen conjugation to crosslinked LMW HA Gels using BDDE as
a crosslinker, conjugation degree is 15 mol %, G' is about 365 Pa.
398.2 mg of LMW HA was hydrated in 1753.24 mg of 1 wt% NaOH in a syringe for
¨ 40min. BDDE (311.7 mg) was added to swollen HA and continue let HA swell for
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another 80 min. The swollen HA/BDDE mixture was pre-reacted at 50 C for 20
min.
801.9 mg of Vitagen was separately dissolved in 1459.7 mg of 10 wt% NaOH and
mixed with HA which was pre-reacted with BDDE. The mixture was continued to
react at 50 C for another 2.5 hrs. After ¨2.5 hours, the HA-Vitagen gel was
formed. Then 195 mg of 12M HCI was added to 9004.0 mg of 10X PBS, pH7.4 to
get HCI-PBS solution and the HCI-PBS solution was added to neutralize and
swell
the gel. The gel was allowed to neutralize and swell over 48 hrs on an orbital
shaker. The gel was sized through a ¨60 pm screen and mixed ¨20 times by
passing back and forth between 2 syringes. The gel was put in a 20,000 MWCO
CE dialysis bag and dialyzed in PBS, pH7.4 buffer. The dialysis went on for
¨120
hours, with frequent change of PBS buffer. After the dialysis, the gel was put
in a
syringe and stored in a 4 C refrigerator. The gel rheological properties were
measured in a procedure as described in Example 3. The conjugation degree was
determined to be about 15 mol% using a similar method as the AA2G
determination as described in Example 2. Gel storage modulus is about 365 Pa.
Example 10: Vitagen conjugation to linear HA via amidization chemistry
200.3 mg of HMW HA was hydrated in 10 ml of water in 60 cc syringe. 500 mg of
Vitagen was dissolved in 0.5 ml of water and solution was neutralized to pH
4.8.
197.7 mg of EDC and 149 mg of NHS were dissolved separately in 6 ml of water.
The above solutions (solutions and EDC/NHS solutions) are added to another 60
cc syringe containing 23.5 ml of water. The two syringes are mixed 20 times by
passing back and forth between 2 syringes. The mixtures was stored in one
syringe and soaked in 37 C bath for 4 hrs. The solutions was finally dialyzed
against PBS pH7.4 buffer until no noticeable Vitagen was observed. The
conjugation degree was determined by a similar method as described Example 3.
The conjugation degree is about 10 mor/o.
Example 11: AA2P Conjugations to crosslinked HA gels
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200.4 mg of LMW HA is hydrated in 1000 mg of MES 5.2 buffer in a syringe for
¨30min. 292 mg of AA2P is put in a vial, followed by 300 mg of star-PEG amine
added. The above solution is allowed to react at room temperature overnight.
The gel was hydrated with PBS buffer and dialyzed against PBS buffer to remove
unreacted AA2P. The finally gel was characterized as described in Examples 2
and 3 to determine the conjugation degree and gel rheological properties. The
conjugation degree is about 20 mol%. The storage modulus (G') is about 500 Pa.
Example 12
Formulation of a HA/BODE Dermal Filler Product with AA2G for
Reducing Appearance of Fine Lines
To any of the gels described in the above Examples, after dialysis, a suitable
amount of free HA gel may be added to the gel to improve of modify gel
cohesivity
and/or injectability. For example, free HA fibers are swollen in a phosphate
buffer
solution, in order to obtain a homogeneous viscoelastic gel ("free" HA gel).
This
uncrosslinked gel is added, before the dialysis step, to the HA/BDDE
crosslinked
gel obtained in Example 1 (for example, to obtain a composition having between
about 1`)/0 to about 5%, w/w free HA). The resulting gel is then filled into
Ready-to-
Fill sterile syringes and autoclaved at sufficient temperatures and pressures
for
sterilization for at least about 1 minute. After autoclaving, the final
HA/AA2G
product is packaged and distributed to physicians to use as a dermal filler
for
superficial injection to improve the appearance of fine lines in the
periorbital or
other facial region.
Example 13
Formulation of HA-AA2G Dermal Filler including Lidocaine
The procedure of Example 12 is followed, but after the dialysis step and
before the
addition of free HA gel, lidocaine chlorhydrate (lidocaine HCI) is added to
the
mixture. The (lidocaine NCI) in powder form may first be solubilized in WFI
and
filtered through a 0.2 pm filter. Dilute NaOH solution is added to the
cohesive
HA/AA2G gel in order to reach a slightly basic pH (for example, a pH of
between
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about 7.5 and about 8). The lidocaine HCI solution is then added to the
slightly
basic gel to reach a final desired concentration, for example, a concentration
of
about 0.3% (w/w). The resulting pH of the HA/AA2G/lidocaine mixture is then
about 7 and the HA concentration is about 24 mg/g. Mechanical mixing is
performed in order to obtain a proper homogeneity in a standard reactor
equipped
with an appropriate blender mechanism.
Example 14
Conjugations of additives containing
carboxyl functional group to HA hydrogels.
Additives such as retinoic acid (AKA, tretinoin), adapalence and alpha-lipoic
acid
contain carboxyl functional group (-COOH). These additives are conjugated to
HA
hydrogels via esterifications using EDC chemistry. An example for the
conjugations in accordance with an embodiment of the invention is described as
follows:
200 mg of HMW HA is hydrated in 10 ml of pH 4.8 MES buffer in 60 cc
syringe. In another syringe, 200 mg of retinoic acid is dissolved in 5 ml of
water-
acetone mixture (water/acetone volume ratio 1:3). The above two syringes are
mixed via a syringe connector for about 20 times. Then 197.7 mg of EDC and 149
mg of NHS are dissolved separately in 6 ml of water in a separate syringe. The
syringe containing EDC and NHS is connected the syringe containing with HA and
retinoic acid to allow reactants to mix at least for 20 times by passing back
and
forth between 2 syringes. The mixtures are stored in one syringe and soaked in
37 C bath for 4 hrs. The gels are dialyzed against isopropanol to remove
unconjugated Retinoic acid, and then dialyzed against PBS buffer under aseptic
conditions. The gels are packaged into sterilized syringes and stored at 4 C.
Example 15
Conjugations of additives containing hydroxyl functional group to HA
hydrogels.
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Additives such as retinol (AKA, tretinoin), catalase, dimethylaminoethanol and
g-
Tocopherol contain hydroxyl functional group (-OH). These additives are
conjugated to HA hydrogels via esterifications using EDC chemistry. A typical
example for the conjugations is described as follows:
200 mg of HMW HA is hydrated in 10 ml of pH 4.8 2-(N-morpholino)
ethanesulfonic acid (MES) buffer in 60 cc syringe. In another syringe, 200 mg
of
retinol acid is dissolved in 5 ml of water-acetone mixture (water/acetone
volume
ratio 1:3). The above two syringes are mixed via a syringe connector for about
20
times. Then 197.7 mg of EDC and 149 mg of NHS are dissolved separately in 6 ml
of water in a separate syringe. The syringe containing EDC and NHS is
connected
the syringe containing with HA and retinol to allow reactants to mix at least
for 20
times by passing back and forth between 2 syringes. The mixtures are stored in
one syringe and soaked in 37 C bath for 4 hrs. The gels are dialyzed against
isopropanol to remove unconjugated retinol, and then dialyzed against PBS
buffer
under aseptic conditions. The gels are packaged into sterilized syringes and
stored at 4 C.
Example 16
Conjugations of additives containing hydroxyl functional group to HA
hydrogels by post-modifications.
This is a two-step process.
Step one: A crosslinked HA gel, for example, a commercial HA-based dermal
filler,
for example, JUVEDERM , Allergan, Irvine CA, or Restylane Medicis Aesthetics,
Inc. is treated with EDC/NHS to activate the carboxyl group of HA.
Step 2: the activated HA hydrogel is treated with additives containing
hydroxyl
groups. Additives containing hydroxyl groups are retinol, catalase,
dimethylaminoethanol and g-Tocopherol hydroxyl functional group (-OH).
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A typical examples for the conjugation of additives to crosslinked HA gels is
as
follows:
2 gm of Juvederm gel is mixed with 200 gm of EDC and 150 mg of NHS at room
temperature. Then 200mg of retinol in 3 ml of acetone-water mixture is added.
The
above mixture is reacted at 37 C for 4 hrs. The gels are dialyzed against
isopropanol to remove unconjugated Retinol, and then dialyzed against PBS
buffer under aseptic conditions. The gels are packaged into sterilized
syringes and
stored at 4 C.
Example 17
Conjugation of growth factors, peptides, or elastin to HA Hvdrogels
Additives such as epidermal growth factor (EGF), transforming growth factor
(TGF) and peptides contain functional amine groups may be conjugated to HA to
form beneficial dermal fillers. These additives are conjugated to HA via
amidization chemistry. A typical example for conjugating is described as
follows:
200.3 mg of HMW HA is hydrated in 10 ml of MES pH 5.4 buffer water. 20 mg of
EGF in 100 mg of MES solution is added. To above mixture, 197.7 mg of EDC
and 149 mg are added. The resulting reaction mixture is allowed to react at 37
C
for 4 hrs. After the reaction completes, the gel is further dialyzed against
isopropanol and then dialyzed against PBS buffer under aseptic conditions. The
gels are packaged into sterilized syringes and stored at 4 C.
The present invention further provides methods of enhancing viability of
grafted
adipose tissue. The methods may generally comprise the steps of introducing a
composition into the skin of a patient adjacent grafted adipose tissue, the
composition being a composition as described elsewhere herein. For example,
the composition may comprise hyaluronic acid and a vitamin C derivative
covalently conjugated to the hyaluronic acid, wherein a degree of conjugation
is
between about 3 mol% and about 40 mol%. In other aspects of the invention,
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methods for treating skin include the steps of introducing, into skin, a
composition
comprising adipose tissue, hyaluronic acid and a vitamin C conjugated to the
hyaluronic acid.
Example 18
Coniuqation of growth factors, peptides, or elastin to HA Hydrogels
To evaluate the mitogenic effects of vitamin C and its derivatives on human
adipose tissue derived stem cells (hASCs), hASCs were cultured on tissue
culture
plastic for 4 days in complete MesenPro medium (Invitrogen, Carlsbad, CA)
supplemented with or without vitamin C (ascorbic acid) or its derivatives
(Vitagen
or AA2G) in free form. Proliferation was assessed by MTT assay as described by
the manufacturer (ATCC, Manassas, VA). After 4 days, concentrations of
ascorbic acid, 0.25, 0.5, and 1mM, were found to enhance proliferation
(measured
by amount of conversion of yellow tetrazolium MTT into purple formazan by
dehydrogenase enzymes (the purple formazon is solubilized by detergent) by
60%, 80%, and 96% above controls lacking ascorbic acid, respectively. Using
the
same concentrations of AA2G yielded proliferation enhancements of 70%, 60%,
and 50% above controls, respectively. Similar results were obtained with
Vitagen,
showing 70%, 60%, and 30% increases over controls, respectively. In summary,
vitamin C and its derivatives, AA2G and vitagen, in the presence of growth
factor
containing media, enhance hASC proliferation in cell culture.
Crosslinked HA gels with conjugated Vitamin C
Preparation of crosslinked HA-based gels with conjugated vitamin C and using
1,4-butaediol diglycidylether (BDDE) as a crosslinker, in accordance with
certain
embodiments of the invention which exhibit reduced Tyndall effect and other
advantages are described in Examples 19 and 20 below. In Example 19, the
vitamin C derivative is ascorbic acid 2-glucoside (AA2G) and in Example 20,
the
vitamin C derivative is ascorbyl 3-aminopropyl phosphate (Vitagen). These gels
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have optimal rheological properties, excellent injectability and high HA
concentration (25 mg/g). Although not wishing to be bound by any specific
theory
of operation, it has been discovered by the present inventors that
crosslinking HA
with BDDE in the presence of either AA2G or Vitagen greatly changes the
properties of the gels, with gels having high crosslinked densities, high HA
concentrations, low viscosities and low extrusion forces, relative to
commercial HA
gels crosslinked with BDDE. Since AA2G or Vitagen is present during
crosslinking, the present gels formed have these ascorbic acid derivatives
coupled
to the HA chains as both pendent groups, and as crosslinkers bridging HA
chains,
either alone, or via BDDE. The microscopic structure of the gel is greatly
changed,
resulting in gels that have very low extrusion force, even through needles as
fine
as 30 gauge. Moreover, the gels have between about 3 mol % to about 10 mor/o,
or up to about 15 mor/o, of vitamin C conjugated to HA. When the gels are
injected, they release active Vitamin C by endogeneous enzymes such as a-
glucosidase from fibroblasts or phosphotase. The active vitamin C may trigger
skin
collagenesis and may act as a radical scavenger to inhibit gel degradation.
Example 19
Formulation of a HA/AA2G gel with reduced Tyndall effect
A mixture of 400.1 mg of LMW HA and 402.3 mg AA2G in a syringe, was hydrated
for 60 min after adding 1764.0 mg of a 5 wt% NaOH solution. In a separate vial
was added 800.8 mg of AA2G, followed by 1401.1 mg of an 9.1 wt% NaOH
solution, and 252.6 mg of BDDE. The resulting solution (pH >12) was allowed to
react in a 50 C water bath for ¨20 min, before it was transferred to the
hydrated
HA. After the addition, the mixture was mixed ¨20 times by passing it back and
forth two syringes. The paste was then transferred in a vial before it was
placed in
a 50 C water bath for ¨2.5 hours. After crosslinking, a solution containing
197.0
mg of 12 M HCI and 9.18 g 10X PBS, pH 7.4 was added to neutralize the base,
and swell the gel for 72 h on an orbital shaker. The gel was sized by forcing
it
through a ¨60 pm pore size mesh. The sized gel was mixed ¨20 times by passing
it back and forth two syringes before it was transferred into a cellulose
ester
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dialysis bag, MWCO ¨ 20 kDa and dialyzed against PBS, pH 7.4 buffer for 5 days
changing the buffer twice daily. After dialysis, the gel was dispensed into 1
ml
COO syringes, centrifuge at 5000 RPM for 5 min to remove air bubbles, and
sterilized with moist steam. The gel had final HA concentration of 25 mg/g, an
AA2G mol% calculated as described in Example 2 of about 10 mol%, and a G' of
about 80 Pa. Other gels were made in a similar manner with G' values of about
60 Pa to about 80 Pa.
Example 19A
Formulation of a HA/AA2G with lidocaine gel with reduced Tyndall effect
To the gel of Example 19, an amount of lidocaine was added to produce a
HA/AA2G with lidocaine gel having 0.3% ww lidocaine. A solution of lidocaine
was prepared by dissolving lidocaine HCI in PBS buffer pH ¨7.4. An aliquot of
the
lidocaine solution was added to the gel in Example 19 after dialysis but
before
sterilization. The gel was then thoroughly mixed to obtain a homogenized
mixture
with a 0.3% w/w lidocaine concentration.
Example 20
Formulation of a HA/Vitagen gel with reduced Tyndall effect
401.0 mg of LMW HA was hydrated in 2355.0 mg of 1 wt% NaOH solution in a
syringe for ¨ 45min. 303.8 mg BDDE of was added to the hydrated HA and mix 10
times by syringe-to-syringe mixing. The mixture was pre-reacted in a 50 C
water
bath for 15 min. 800.1 mg of Vitagen was separately dissolved in 950.6 mg of
15
wt% NaOH, followed by 510.1 Milli-Q water. The Vitagen solution was mixed with
the pre-heated hydrated HA/BDDE mixture 30 times back and forth using syringe-
to-syringe mixing. The mixture was placed back in the 50 C water bath and the
reaction proceeded for another 2 h after which a solution containing 148.1 mg
of
12M HCI and 8523.1 mg of 10X PBS, pH7.4 was added to the cross The HCI-PBS
solution was added to neutralize and swell the gel. The gel was allowed to
neutralize and swell over 48 hrs on an orbital shaker. The gel was sized
through a
¨60 pm screen and mixed ¨20 times by passing back and forth between 2
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syringes. The gel was put in a 20,000 MWCO CE dialysis bag and dialyzed in
PBS, pH7.4 buffer. The dialysis went on for ¨197 hours, with frequent change
of
PBS buffer. After the dialysis, the gel was transferred into 1ml COC syringes,
centrifuge at 5000RPM for 5 min, and sterilized with moist steam. The final HA
concentration of the gel was 24 mg/g.
Crosslinked HA gels via 1-ethyl-343-dimethylaminopropyllcarbodiimide
hydrochloride (EDC) Chemistry
Preparation of crosslinked HA-based gels, in accordance with certain
embodiments of the invention which exhibit reduced Tyndall effect and other
advantages are described in Examples 21 and 22 below. In Example 21, the gel
is made via EDC chemistry using crosslinker is hexamethylene diamine (HMDA),
and in Example 20, 3-[3-(3-amino propoxy)-2,2-bis(3-amino-propoxymethyl)-
propoxy]-propylamine (4 arm amine-4 AA). Crosslinking is carried out under
mild
conditions, e.g. room temperature, and for example, at pH 5.4. The reactions
conditions could be tuned to prepare highly reticulate gels with optimal gel
properties, excellent injectability and high final HA concentrations (¨ 24
mg/g). It
has been discovered by the inventors that it may be advantageous to crosslink
HA
at very low hydration or reaction concentrations, with a moderate amount of
either
HMDA or 4 AA, in conjunction with 1-ethyl-3-(3-dimethylaminopropyl)
carbodiimide
hydrochloride (EDC) and N-hydroxysuccinimide (NHS) or sulfonyl-NHS (sulfo-
NHS), the coupling agents. The gels will have crosslinked points that are far
from
each other hence highly crosslinked materials which have high damping force.
In
contrast, crosslinking of HA with BDDE at such low hydration or reaction
concentrations may be impracticable because of the relative inefficiency of
the
crossl in ker.
Example 21
Formulation of a HA/HMDA gel with reduced Tyndall effect
20.0 g of 100 mM MES buffer pH 5.2 was added to a syringe containing 1000.0
mg of LMW HA. HMDA solution was prepared by dissolving 260.9 mg HMDA.HCI
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in 2010.5 mg of 100 mM MES buffer pH 5.2, and adding 2 pl of 1 M NaOH to bring
pH to 5.2. EDC solution was prepared by dissolving 254.2 mg of EDC in 1188.4
mg 100 mM MES buffer pH 5.2, and in a separate vial, 44.3 mg of NHS was
dissolved in 1341.8 mg of 100 mM MES buffer pH 5.2. Upon full hydration of the
HA, ¨ 1 h, 790 pl of the HMDA solution was added to the hydrated HA. The
mixture was homogenized by 10 times syringe-to-syringe mixing. 490 pl EDC and
490 pl NHS solutions were then added to the homogenized paste and again mix
times by syringe-to-syringe mixing. The mixture was then transferred to a vial
and crosslinked at room temperature for 5 h. before the addition of 17.9 ml of
1X
10 PBS buffer pH 7.4. The gel was allowed to swell for 3 days on a roller
before it
was force through a 60 pm pore size mesh. The sized gel was placed in a
cellulose ester membrane dialysis tubing MWCO 20 KDa and dialyzed against lx
PBS for 4 days changing the buffer twice a day. The gel was dispensed in 1 ml
COC syringes, centrifuge at 5000 RPM for 5 min, and sterilized with moist
steam.
The final HA concentration of the gel was 25 mg/g.
Example 22
Formulation of a HA/4 AA gel with reduced Tyndall effect
32.55 g of 100 mM MES buffer pH 5.2 was added to a syringe containing 1000.4
mg of LMW HA. 4 AA solution was prepared by dissolving 256.3 mg 4 AA in
1039.8 mg of 100 mM MES buffer pH 5.2, and adding 380 pl of 6 M HCI to bring
pH to 5.2. EDC solution was prepared by dissolving 251.2 mg of EDC in 1013.8
mg 100 mM MES buffer pH 5.2, and in a separate vial, 74.7 mg of NHS was
dissolved in 2020.0 mg of 100 mM MES buffer pH 5.2. Upon full hydration of the
HA, ¨ 1 h, 260 pl of the 4 AA solution was added to the hydrated HA. The
mixture
was homogenized by 10 times syringe-to-syringe mixing. 277 pl EDC and 273 pl
NHS solutions were then added to the homogenized paste and again mix 10 times
by syringe-to-syringe mixing. The mixture was then transferred to a vial and
crosslinked at room temperature for 5 h. before the addition of 6.4 ml of 10X
PBS
buffer pH 7.4. The gel was allowed to swell for 3 days on a roller before it
was
force through a 60 pm pore size mesh. The sized gel was placed in a cellulose
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ester membrane dialysis tubing MWCO 20 KDa and dialyzed against 1X PBS for 4
days changing the buffer twice a day. The gel was dispensed in 1 ml COO
syringes, centrifuge at 5000 RPM for 5 min, and sterilized with moist steam.
The
gel had a final HA concentration of 23 mg/g.
Example 23
Determination of rheoloqical properties of gels of Examples 19-22.
An Oscillatory parallel plate rheometer, Anton Paar Physica MCR 301, was used
to measure the rheological properties of the gels. A plate diameter of 25 mm
was
used at a gap height of 1 mm. Measurements were done at a constant
temperature of 25 C. Each measurement consisted of a frequency sweep from 1
to 10 Hz at a constant strain of 2% and a logarithmic increase of frequency
followed by a strain sweep from 1 to 300% at a constant frequency of 5 Hz with
a
logarithmic increase in strain. The storage modulus (G') and the viscose
modulus
(G") were obtained from the strain sweep at 1% strain.
Storage and viscous moduli of gels obtained from Examples 19-22
Sample ID Storage Modulus (G') Pa Viscous Modulus (G") Pa
Example 19 84 25
Example 20 83 33.7
Example 21 67 42
Example 22 41 29.5
Example 24
Extrusion force measurements of gels of Examples 19-22
The force required to extrude the gels through a 30 gauge needle was measured
using an Instron 5564 and a Bluehill 2 software. The gels were extruded from a
1
ml COO syringe through a 30G% TSK needle. The plunger was pushed at a speed
of 100 mm/min for 11.35 mm, and the extrusion force was recorded.
Extrusion force of gels obtained from Examples 19-22
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Sample ID Extrusion force (N)
Example 19 25
Example 20 24
Example 21 22
Example 22 19.5
Example 25
Biocompatibilitv testing of gels of Examples 19-22
50 pl bolus injections of gel were implanted intradermally in the dorsal
surface of
Sprague Dawley rats. The implants were removed at 1 week and analyzed by
histology with hematoxylin and eosin (H&E) staining, and CD68 staining which
is a
marker for mononuclear inflammation cells. Three 20X images of CD68 were
scored from 0 ¨ 4 based on the degree of staining. These values were then
averaged out to give a sample score. Four samples were analyzed from each gel.
Average CD68 scores of Examples 19-22
Sample ID Score
Example 1 1.8
Example 2 1.6
Example 3 2.7
Example 4 1.3
Example 26
Cvtotoxicitv testing of gels of Examples 19-22, ISO 10993-5.
In Vitro cytotoxicity tests of the gels were performed by NAMSA according to
the
Agarose Overlay Method of ISO 10993-5: biological Evaluation of Medical
Devices
¨ Part 5: Tests for In Vitro Cytotoxicity. Triplicate wells were dosed with
0.1 ml of
test articles placed on a filtered disc, as well as 0.9% NaCI solution, 1 cm
length of
high density polyethylene as a negative control, and 1 x 1 cm2 portion of
latex as a
positive control. Each was placed on an agarose surface directly overlaying a
monolayer of L929 mouse fibroblast cells. After incubating at 37 C in 5% CO2
for
24 h. the cultures were examined macroscopically and microscopically for any
abnormal cell morphology and cell lysis. The test articles were scored from 0
¨ 4
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based on the zone of lysis in the proximity of the samples. Test materials
from
examples 1, 3, and 4 scored 0 as test articles showed no evidence of causing
any
cell lysis or toxicity.
Quantitative Analysis of Tyndall effect
In order to further support visual observations and carry out comparative
performance analysis of HA fillers, it was deemed necessary to do a
quantitative
analysis of Tyndall effect. As such no quantitative techniques for Tyndall
effect
specific to dermal fillers exist in the literature. However, based on existing
scientific understanding on light scattering and interaction of light with
skin, two
distinct approaches based on (a) colorimetry, and (b) spectroscopy were
employed to quantify Tyndall effect in skin. Based on these techniques three
distinct quantitative parameters (outlined below) were defined to measure
Tyndall
effect in vivo.
a) Tyndall Effect Visual Score: The scale had a range of 1 to 5 with
increments of
0.5. A score of 1 was given to injection sites with normal skin tone and no
blue
discoloration. A maximum score of 5 was given to thick and pronounced blue
discoloration (typically associated with Restylane or Juvederm Ultra Plus).
Three
independent observers were trained on the scale before being blinded to score
test samples.
b) Blue component of skin color ¨ "b": A chromameter (CM2600D, Konica
Minolta, NJ) was used to quantify the blue color component of light remitted
from
skin sites injected with the various fillers. This was achieved by using the
"b"
component of L-a-b color scale.
c) "% Blue Light" remitted from skin: A portable spectrophotometer (CM2600D,
Konica Minolta, NJ) was used to quantify the (:)/0 blue light remitted from
skin in the
total visible light range. This was achieved by integrating the area under the
visible
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light spectrum between 400-490nm and normalizing it by the total area under
the
spectrum (400-700nm).
Example 27
Tyndall evaluation of gels
Gels were injected intradermally through a 27G% TSK needle using linear
threading technique into the thighs of two months old hairless rats. The gels
were
implanted superficially to mimic clinical fine line procedures. Tests for
Tyndall were
performed 48 h after gel implantation. Before performing the Tyndall tests,
the
animals were euthanized to improve contrast of the Tyndall effect due to lack
of
hemoglobin.
Images of gels from Examples 19 and 21, 2 days after implantation, are shown
in
Figure 12. Images for commercial Juvederm Refine and Restylane Touch are also
shown for comparison. A bluish line (Tyndall effect) is clearly visible in the
images
of commercial gels Juvederm Refine and Restylane Touch . Gels from Examples
19, 19A (not shown) and 21 exhibited no Tyndall effect.
A visual score of 1 ¨ 5 with increments of 0.5, was used to score the
injection
sites. Injection sites with score of 1 showed no skin discoloration, while
injections
sites with score of 5 showed severe blue discoloration of the skin.
Spectroscopic
analyses were also performed on the injection sites with the aid of a
chromatometer (CM2600D, Konica Minolta, NJ). The blue component of skin color
"b", and the (:)/0 of blue light remitted from skin (400 ¨ 700 nm) were
independently
measured. Figures 13 and 14, show visual Tyndall score and (:)/0 of blue light
remitted. Gels from Examples 19 and 21 showed no Tyndall effect, and had lower
visual Tyndall score and (:)/0 of blue light remitted values. The Tyndall
score and (:)/0
of remitted blue light values were higher for Juvederm Refine and Restylane
Touch. Belotero Soft did not show any Tyndall and values were comparable to
those of Examples 19 and 21. See Figures 13 and 14.
Example 28
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In vivo duration evaluation of gels by histology
50 pl bolus injections of gels of the invention and commercial gels were
implanted
intradermally in the dorsal surface of Sprague Dawley rats. The implants were
removed at 1 week and analyzed by histology with hematoxylin and eosin (H&E)
staining. Sections were taken at exactly at the injection sites. Two sections
were
cut from each tissue sample and the H&E stained section was stitched using a
stitching scope. The samples were then grouped and scored as follows; none
(0%), low (25%), medium (50%), and high (100%) depending on the amount of
material remaining. See Figure 15.
Example 28A
In vivo duration evaluation of gels by MRI
Magnetic Resonance Imaging (MRI) study was used to evaluate the volume and
surface area change with time of gels of t he invention and commercial gels
over a
period of 40 weeks, after intradermal injections in female Sprague-Dawley
rats.
The gels were injected at a target volume of 150 pl per implant. Implants were
located at two contralateral sites slightly caudal to shoulder, two
contralateral sites
slightly rostral from knee, and two contralateral sites midpoint between head
and
tail. MRI scans were performed on a 7 Tesla 70/30 Bruker Biospec MRI scanner.
Images were collected on the day of implantation (week 0), and at 12, 24, 40
weeks after implantation. Plots of absolute volume of gel versus Time is shown
in
Figure 16 below. High persistence gels have high absolute volume at 40 weeks
implantation.
Example 29
Compositions of the invention as used in the treatment of periorbital lines
A 40 year old thin woman presents with fine wrinkles in the periorbital region
and
requests dermal filler treatment. Using a 30 gauge needle, the physician
introduces 0.6 ml of a HA-based gel in accordance with the invention (such as
that
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described in Example 19) superficially into the fine lines beneath each of her
eyes
and in the tear trough region using linear threading technique. Although the
gel is
introduced superficially, no blue discoloration is observed and the patient is
satisfied with the results.
As shown, compositions of the present invention, for example, those of
Examples 19 and 21, have reduced or insignificant Tyndall effect, and
substantially longer duration in the body relative to certain HA-based
commercial
gels, for example, Juvederm Refine/Surgiderm 18 and Belotero Soft. For
example, relative to commercial "fine line" formulation Belotero Soft, Example
19
of the present invention had not only a Tyndall score at least as favorable as
this
commercial gel, but advantageously exhibited substantially higher in vivo
duration.
Example 30
Injectable compositions of the invention
for improvement of the appearance of fine lines
Additives such as Vitamin A, Vitamin B, Vitamin C, Vitamin D, Vitamin E and
derivatives thereof, alone and in combination, are conjugated to crosslinked
hyaluronic acid gels in a manner so as to produce a variety of substantially
optically transparent, injectable HA-based gels. The HA component is at least
90%
by weight, for example, is substantially entirely low molecular weight HA, or
about
100% low molecular weight HA, as defined elsewhere herein. These additives
are conjugated to HA hydrogels using any suitable means. The conjugated gels
are sized and processed to produce an injectable, pH neutral, cohesive
composition having a HA concentration of at least about 20 mg/g, for example,
about 23, about 24 mg/g, about 25 mg/g, up to about 30 mg/g, and suitable for
injection through a fine gauge needle. The gels have a G' value of at least
about
50 PA, about 60 Pa, about 70 Pa, about 80 Pa up to, and no greater than about
100 Pa. The gels are packaged and sterilized using autoclave, UV light or
other
suitable means.
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= =
Each of the gels is useful for superficial injection, for example, injection
into skin at
a depth of no greater than about 1.0mm, in a wrinkle of patients, for example,
the
periorbital region, nasolabial fold region, tear trough region, neck region,
or any
other facial region that would benefit from dermal filling. Despite the
superficial
introduction of the gels, no discoloration due to Tyndall effect is observed
and the
patients are satisfied with the results.
In closing, it is to be understood that although aspects of the present
specification
have been described with reference to the various embodiments, one skilled in
the
art will readily appreciate that the specific examples disclosed are only
illustrative
of the principles of the subject matter disclosed herein.
20
Certain embodiments of this invention are described herein, including the best
mode known to the inventors for carrying out the invention. Of course,
variations
on these described embodiments will become apparent to those of ordinary skill
in
the art upon reading the foregoing description. The inventor expects skilled
artisans to employ such variations as appropriate, and the inventors intend
for the
invention to be practiced otherwise than specifically described herein.
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Accordingly, this invention includes all modifications and equivalents of the
subject
matter recited in the claims appended hereto as permitted by applicable law.
Moreover, any combination of the above-described elements in all possible
variations thereof is encompassed by the invention unless otherwise indicated
herein or otherwise clearly contradicted by context.
Groupings of alternative elements or embodiments of the invention disclosed
herein are not to be construed as limitations. Each group member may be
referred to and claimed individually or in any combination with other members
of
the group or other elements found herein. It is anticipated that one or more
members of a group may be included in, or deleted from, a group for reasons of
convenience and/or patentability. When any such inclusion or deletion occurs,
the
specification is deemed to contain the group as modified thus fulfilling the
written
description of all Markush groups used in the appended claims.
Unless otherwise indicated, all numbers expressing quantities of ingredients,
properties such as molecular weight, reaction conditions, and so forth used in
the
specification and claims are to be understood as being modified in all
instances by
the term "about." As used herein, the term "about" means that the item,
parameter
or term so qualified encompasses a range of plus or minus ten percent above
and
below the value of the stated item, parameter or term. Accordingly, unless
indicated to the contrary, the numerical parameters set forth in the
specification
and attached claims are approximations that may vary depending upon the
desired properties sought to be obtained by the present invention. At the very
least, and not as an attempt to limit the application of the doctrine of
equivalents to
the scope of the claims, each numerical parameter should at least be construed
in
light of the number of reported significant digits and by applying ordinary
rounding
techniques. Notwithstanding that the numerical ranges and parameters setting
forth the broad scope of the invention are approximations, the numerical
values
set forth in the specific examples are reported as precisely as possible. Any
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=
numerical value, however, inherently contains certain errors necessarily
resulting
from the standard deviation found in their respective testing measurements.
The terms "a," "an," "the" and similar referents used in the context of
describing
the invention (especially in the context of the following claims) are to be
construed
to cover both the singular and the plural, unless otherwise indicated herein
or
clearly contradicted by context. Recitation of ranges of values herein is
merely
intended to serve as a shorthand method of referring individually to each
separate
value falling within the range. Unless otherwise indicated herein, each
individual
value is incorporated into the specification as if it were individually
recited herein.
All methods described herein can be performed in any suitable order unless
otherwise indicated herein or otherwise clearly contradicted by context. The
use
of any and all examples, or exemplary language (e.g., "such as") provided
herein
is intended merely to better illuminate the invention and does not pose a
limitation
on the scope of the invention otherwise claimed. No language in the
specification
should be construed as indicating any non-claimed element essential to the
practice of the invention.
Specific embodiments disclosed herein may be further limited in the claims
using
consisting of or consisting essentially of language. When used in the claims,
whether as filed or added per amendment, the transition term "consisting of"
excludes any element, step, or ingredient not specified in the claims. The
transition term "consisting essentially of" limits the scope of a claim to the
specified
materials or steps and those that do not materially affect the basic and novel
characteristic(s). Embodiments of the invention so claimed are inherently or
expressly described and enabled herein.
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