U.S. patent application number 10/957910 was filed with the patent office on 2005-05-26 for drug delivery device.
Invention is credited to Yaacobi, Yoseph.
Application Number | 20050112175 10/957910 |
Document ID | / |
Family ID | 22577913 |
Filed Date | 2005-05-26 |
United States Patent
Application |
20050112175 |
Kind Code |
A1 |
Yaacobi, Yoseph |
May 26, 2005 |
Drug delivery device
Abstract
Drug delivery devices, and methods of delivering
pharmaceutically active agents to a target tissue within a body
using such devices, are disclosed. One drug delivery device
includes a body having an internal surface for placement proximate
a target tissue and a well having an opening to the internal
surface. An inner core comprising a pharmaceutically active agent
is disposed in the well.
Inventors: |
Yaacobi, Yoseph; (Fort
Worth, TX) |
Correspondence
Address: |
ALCON RESEARCH, LTD.
R&D COUNSEL, Q-148
6201 SOUTH FREEWAY
FORT WORTH
TX
76134-2099
US
|
Family ID: |
22577913 |
Appl. No.: |
10/957910 |
Filed: |
October 4, 2004 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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10957910 |
Oct 4, 2004 |
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10186960 |
Jul 1, 2002 |
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6808719 |
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10186960 |
Jul 1, 2002 |
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09660000 |
Sep 12, 2000 |
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6413540 |
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60160673 |
Oct 21, 1999 |
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Current U.S.
Class: |
424/427 ;
514/171 |
Current CPC
Class: |
A61F 9/0017 20130101;
A61P 27/02 20180101; A61K 9/0051 20130101 |
Class at
Publication: |
424/427 ;
514/171 |
International
Class: |
A61K 031/57; A61F
002/00 |
Claims
What is claimed is:
1. An ophthalmic drug delivery device, comprising: a body having: a
scleral surface having a radius of curvature that facilitates
contact with a sclera of a human eye; a well having an opening to
said scleral surface; and a geometry that facilitates disposing
said device on an outer surface of said sclera, below a Tenon's
capsule of said eye, and in a posterior segment of said eye; and an
inner core disposed in said well and comprising a pharmaceutically
active agent.
2. The ophthalmic drug delivery device of claim 1, wherein said
body has a geometry that facilitates disposing said device on said
outer surface of said sclera, below said Tenon's capsule, and in
said posterior segment so that said inner core is disposed
proximate a macula of said eye.
3. The ophthalmic drug delivery device of claim 2, wherein said
body has a geometry that facilitates disposing said device on said
outer surface of said sclera, below said Tenon's capsule, and in
said posterior segment so that said inner core is disposed
generally above said macula.
4. The ophthalmic drug delivery device of claim 1, wherein said
inner core is a tablet.
5. The ophthalmic drug delivery device of claim 4, wherein at least
a portion of said body is made from a generally elastic material so
that said generally elastic material, a geometry of said well, and
a geometry of said tablet frictionally secure said tablet within
said well.
6. The ophthalmic drug delivery device of claim 4, wherein said
tablet is formulated to bioerode and release said pharmaceutically
active agent at a controlled rate.
7. The ophthalmic drug delivery device of claim 1, wherein said
inner core is a hydrogel.
8. The ophthalmic drug delivery device of claim 7, wherein said
hydrogel is formulated to bioerode and release said
pharmaceutically active agent at a controlled rate.
9. The ophthalmic drug delivery device of claim 7, wherein said
pharmaceutically active agent diffuses through said hydrogel at a
controlled rate.
10. The ophthalmic drug delivery device of claim 1, further
comprising a retaining member extending from said body proximate
said opening, and wherein said retaining member helps to retain
said inner core in said well.
11. The ophthalmic drug delivery device of claim 10, wherein said
retaining member comprises a rim at least partially disposed around
said opening.
12. The ophthalmic drug delivery device of any one of claims 1-11,
wherein said pharmaceutically active agent comprises a compound
selected from the group consisting of
4,9(11)-Pregnadien-17.alpha.,21-diol-3,20-dione and
4,9(11)-Pregnadien-17.alpha.,21-diol-3,20-dione-21-acetate.
13. The ophthalmic drug delivery device of any one of claims 1-11,
wherein said pharmaceutically active agent comprises eliprodil.
Description
[0001] This application is a continuation of U.S. application Ser.
No. 10/186,960, filed Jul. 1, 2002, which is a continuation of U.S.
application Ser. No. 09/660,000, filed Sep. 12, 2000, now U.S. Pat.
No. 6,413,540, which claims priority from U.S. Provisional
Application No. 60/160,673, filed Oct. 21, 1999.
FIELD OF THE INVENTION
[0002] The present invention generally pertains to biocompatible
implants for localized delivery of pharmaceutically active agents
to body tissue. More particularly, but not by way of limitation,
the present invention pertains to biocompatible implants for
localized delivery of pharmaceutically active agents to the
posterior segment of the eye.
DESCRIPTION OF THE RELATED ART
[0003] Several diseases and conditions of the posterior segment of
the eye threaten vision. Age related macular degeneration (ARMD),
choroidal neovascularization (CNV), retinopathies (i.e. diabetic
retinopathy, vitreoretinopathy), retinitis (i.e. cytomegalovirus
(CMV) retinitis), uveitis, macular edema, and glaucoma are several
examples.
[0004] Age related macular degeneration (ARMD) is the leading cause
of blindness in the elderly. ARMD attacks the center of vision and
blurs it, making reading, driving, and other detailed tasks
difficult or impossible. About 200,000 new cases of ARMD occur each
year in the United States alone. Current estimates reveal that
approximately forty percent of the population over age 75, and
approximately twenty percent of the population over age 60, suffer
from some degree of macular degeneration. "Wet" ARMD is the type of
ARMD that most often causes blindness. In wet ARMD, newly formed
choroidal blood vessels (choroidal neovascularization (CNV)) leak
fluid and cause progressive damage to the retina.
[0005] In the particular case of CNV in ARMD, two main methods of
treatment are currently being developed, (a) photocoagulation and
(b) the use of angiogenesis inhibitors. However, photocoagulation
can be harmful to the retina and is impractical when the CNV is
near the fovea. Furthermore, photocoagulation often results in
recurrent CNV over time. Oral or parenteral (non-ocular)
administration of anti-angiogenic compounds is also being tested as
a systemic treatment for ARMD. However, due to drug-specific
metabolic restrictions, systemic administration usually provides
sub-therapeutic drug levels to the eye. Therefore, to achieve
effective intraocular drug concentrations, either an unacceptably
high dose or repetitive conventional doses are required. Periocular
injections of these compounds often result in the drug being
quickly washed out and depleted from the eye, via periocular
vasculature and soft tissue, into the general circulation.
Repetitive intraocular injections may result in severe, often
blinding, complications such as retinal detachment and
endophthalmitis.
[0006] In order to prevent complications related to the
above-described treatments and to provide better ocular treatment,
researchers have suggested various implants aimed at localized
delivery of anti-angiogenic compounds to the eye. U.S. Pat. No.
5,824,072 to Wong discloses a non-biodegradable polymeric implant
with a pharmaceutically active agent disposed therein. The
pharmaceutically active agent diffuses through the polymer body of
the implant into the target tissue. The pharmaceutically active
agent may include drugs for the treatment of macular degeneration
and diabetic retinopathy. The implant is placed substantially
within the tear fluid upon the outer surface of the eye over an
avascular region, and may be anchored in the conjunctiva or sclera;
episclerally or intrasclerally over an avascular region;
substantially within the suprachoroidial space over an avascular
region such as the pars plana or a surgically induced avascular
region; or in direct communication with the vitreous.
[0007] U.S. Pat. No. 5,476,511 to Gwon et al. discloses a polymer
implant for placement under the conjunctiva of the eye. The implant
may be used to deliver neovascular inhibitors for the treatment of
ARMD and drugs for the treatment of retinopathies, retinitis, and
CMV retinitis. The pharmaceutically active agent diffuses through
the polymer body of the implant.
[0008] U.S. Pat. No. 5,773,019 to Ashton et al. discloses a
non-bioerodable polymer implant for delivery of certain drugs
including angiostatic steroids and drugs such as cyclosporine for
the treatment of uveitis. Once again, the pharmaceutically active
agent diffuses through the polymer body of the implant.
[0009] All of the above-described implants require careful design
and manufacture to permit controlled diffusion of the
pharmaceutically active agent through a polymer body (matrix
devices) or polymer membrane (reservoir devices) to the desired
site of therapy. Drug release from these devices depends on the
porosity and diffusion characteristics of the matrix or membrane,
respectively. These parameters must be tailored for each drug
moiety to be used with these devices. Consequently, these
requirements generally increase the complexity and cost of such
implants.
[0010] U.S. Pat. No. 5,824,073 to Peyman discloses an indentor for
positioning in the eye. The indentor has a raised portion that is
used to indent or apply pressure to the sclera over the macular
area of the eye. This patent discloses that such pressure decreases
choroidal congestion and blood flow through the subretinal
neovascular membrane, which, in turn, decreases bleeding and
subretinal fluid accumulation.
[0011] Therefore, a need exists in the biocompatible implant field
for a surgically implantable drug delivery device capable of safe,
effective, rate-controlled, localized delivery of a wide variety of
pharmaceutically active agents to any body tissue. The surgical
procedure for implanting such a device should be safe, simple,
quick, and capable of being performed in an outpatient setting.
Ideally, such a device should be easy and economical to
manufacture. Furthermore, because of its versatility and capability
to deliver a wide variety of pharmaceutically active agents, such
an implant should be capable of use in clinical studies to deliver
various agents that create a specific physical condition in a
patient or animal subject. In the particular field of ophthalmic
drug delivery, such an implantable drug delivery device is
especially needed for localized delivery of pharmaceutically active
agents to the posterior segment of the eye to combat ARMD, CNV,
retinopathies, retinitis, uveitis, macular edema, and glaucoma.
SUMMARY OF THE INVENTION
[0012] One aspect of the present invention comprises a drug
delivery device including a body having an internal surface for
placement proximate a target tissue and a well having an opening to
the internal surface. An inner core comprising a pharmaceutically
active agent is disposed in the well.
[0013] In another aspect, the present invention comprises a method
of delivering a pharmaceutically active agent to a target tissue
within a body. A drug delivery device is provided. The drug
delivery device includes a body having an internal surface and a
well having an opening to the internal surface, and an inner core
disposed in the well comprising a pharmaceutically active agent.
The device is disposed within the body so that the pharmaceutically
active agent is in communication with the target tissue through the
opening.
[0014] In a further aspect, the present invention comprises an
ophthalmic drug delivery device including a body having a scleral
surface for placement proximate a sclera and a well or cavity
having an opening to the scleral surface. An inner core comprising
a pharmaceutically active agent is disposed in the well.
[0015] In a further aspect, the present invention comprises a
method of delivering a pharmaceutically active agent to an eye
having a sclera. A drug delivery device is provided. The drug
delivery device includes a body having a scleral surface and a well
having an opening to the scleral surface, and an inner core
disposed in the well comprising a pharmaceutically active agent.
The device is disposed within the eye so that the pharmaceutically
active agent is in communication with the sclera through the
opening.
[0016] In a further aspect, the present invention comprises a
method of delivering a pharmaceutically active agent to an eye
having a sclera, a Tenon's capsule, and a macula. A drug delivery
device comprising a body having a pharmaceutically active agent
disposed therein is provided. The device is disposed on an outer
surface of the sclera, below the Tenon's capsule, and proximate the
macula.
BRIEF DESCRIPTION OF THE DRAWINGS
[0017] For a more complete understanding of the present invention,
and for further objects and advantages thereof, reference is made
to the following description taken in conjunction with the
accompanying drawings in which:
[0018] FIG. 1 is a side sectional view of a drug delivery device
according to a preferred embodiment of the present invention;
[0019] FIG. 2 is a side sectional view of a second drug delivery
device according to a preferred embodiment of the present
invention;
[0020] FIG. 3 is a side sectional view schematically illustrating
the human eye;
[0021] FIG. 4 is detailed cross-sectional view of the eye of FIG. 3
along line 4-4;
[0022] FIG. 5 is a perspective view of an ophthalmic drug delivery
device according to a preferred embodiment of the present
invention;
[0023] FIG. 6A is a side sectional view of the ophthalmic drug
delivery device of FIG. 5;
[0024] FIG. 6B is an enlarged cross-sectional view of the
ophthalmic drug delivery device of FIG. 6A taken along line 6B-6B;
and
[0025] FIG. 7 is a graphical illustration of the results of a
pharmacokinetic study with New Zealand White rabbits implanted with
the ophthalmic drug delivery device of FIGS. 5 through 6B showing
the mean concentration of a pharmaceutically active agent at a
target site in the retina and choroid of the rabbits as a function
of time.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0026] The preferred embodiments of the present invention and their
advantages are best understood by referring to FIGS. 1 through 7 of
the drawings, like numerals being used for like and corresponding
parts of the various drawings.
[0027] FIG. 1 schematically illustrates a drug delivery device 10
according to a preferred embodiment of the present invention.
Device 10 may be used in any case where localized delivery of a
pharmaceutically active agent to body tissue is required. By way of
example, device 10 may be used to treat a medical disorder of the
eye, ear, nose, throat, skin, subcutaneous tissue, or bone. Device
10 may be used in humans or animals.
[0028] Device 10 generally includes a body 12 having an internal
surface 14 and an external surface 16. As shown in FIG. 1, body 12
preferably has a generally rectangular three-dimensional geometry
with a proximal end 18 and a distal end 20. Body 12 may have any
other geometry that has an internal surface 14 for placement
proximate a target tissue in the body of a patient. By way of
example, body 12 may have a cylindrical, an oval, a square, or
other polygonal three-dimensional geometry.
[0029] Body 12 includes a well or cavity 22 having an opening 24 to
internal surface 14. An inner core 26 is preferably disposed in
well 22. Inner core 26 is preferably a tablet comprising one or
more pharmaceutically active agents. Alternatively, inner core 26
may comprise a conventional hydrogel having one or more
pharmaceutically active agents disposed therein. A retaining member
28 is preferably disposed proximate opening 24. Retaining member 28
prevents inner core 26 from falling out of well 22. When inner core
26 is a cylindrical tablet, retaining member 28 is preferably a
continuous rim or lip disposed circumferentially around opening 24
having a diameter slightly less than the diameter of tablet 26.
Alternatively, retaining member 26 may comprise one or more members
that extend from body 12 into opening 24. Although not shown in
FIG. 1, inner core 26 may alternatively comprise a suspension,
solution, powder, or combination thereof containing one or more
pharmaceutically active agents. In this embodiment, internal
surface 14 is formed without opening 24, and the suspension,
solution, powder, or combination thereof diffuses through the
relatively thin portion of internal surface 14 below inner core 26.
Still further in the alternative, device 10 may be formed without
well 22 or inner core 26, and the pharmaceutically active agent(s)
in the form of a suspension, solution, powder, or combination
thereof may be dispersed throughout body 12 of device 10. In this
embodiment, the pharmaceutically active agent diffuses through body
12 into the target tissue.
[0030] The geometry of device 10 maximizes communication between
the pharmaceutically active agent of inner core 26 and the tissue
underlying internal surface 14. Internal surface 14 preferably
physically contacts the target tissue. By way of example, if the
target tissue has a generally flat surface, device 10 would be
appropriate for the delivery of a pharmaceutically active agent. As
another example, if the target tissue has a generally convex
surface, a device 10a shown in FIG. 2 having a generally concave
internal surface 14a designed to mate with such a target surface
may be utilized. Corners 30 of proximal end 18a, and corners 32 of
distal end 20a, may be slanted and/or rounded off to facilitate
surgical placement of device 10a and to maximize comfort to the
patient. Retaining member 28 is preferably designed with a minimum
thickness necessary to retain inner core 26 so as to dispose a
surface 26a of inner core 26 in close proximity to the target
tissue. Although not shown in FIG. 1 or 2, inner core 26 may be
formed so that surface 26a physically contacts the target
tissue.
[0031] Alternatively, device 10 or 10a may be disposed in the body
of a patient so that internal surface 14 or 14a is disposed
proximate the target tissue. In this case, internal surface 14 or
14a physically contacts intermediate tissue disposed between it and
the target tissue. The pharmaceutically active agent of inner core
26 communicates with the target tissue through opening 24 and this
intermediate tissue.
[0032] Referring again to FIG. 1, body 12 preferably comprises a
biocompatible, non-bioerodable material. Body 12 more preferably
comprises a biocompatible, non-bioerodable polymeric composition.
Said polymeric composition may be a homopolymer, a copolymer,
straight, branched, cross-linked, or a blend. Examples of polymers
suitable for use in said polymeric composition include silicone,
polyvinyl alcohol, ethylene vinyl acetate, polylactic acid, nylon,
polypropylene, polycarbonate, cellulose, cellulose acetate,
polyglycolic acid, polylactic-glycolic acid, cellulose esters,
polyethersulfone, acrylics, their derivatives, and combinations
thereof. Examples of suitable soft acrylics are more fully
disclosed in U.S. Pat. No. 5,403,901, which is incorporated herein
in its entirety by reference. Said polymeric composition most
preferably comprises silicone. Of course, said polymeric
composition may also comprise other conventional materials that
affect its physical properties, including, but not limited to,
porosity, tortuosity, permeability, rigidity, hardness, and
smoothness. Exemplary materials affecting certain ones of these
physical properties include conventional plasticizers, fillers, and
lubricants. Said polymeric composition may comprise other
conventional materials that affect its chemical properties,
including, but not limited to, toxicity, hydrophobicity, and body
12--inner core 26 interaction. Body 12 is preferably impermeable to
the pharmaceutically active agent of inner core 26. When body 12 is
made from a generally elastic polymeric composition, the diameter
of well 22 may be slightly less than the diameter of inner core 26.
This frictional fit secures inner core 26 within well 22. In this
embodiment, body 12 may be formed without retaining member 28, if
desired.
[0033] Inner core 26 may comprise any pharmaceutically active
agents suitable for localized delivery to a target tissue. Examples
of pharmaceutically active agents suitable for inner core 26 are
anti-infectives, including, without limitation, antibiotics,
antivirals, and antifungals; antiallergenic agents and mast cell
stabilizers; steroidal and non-steroidal anti-inflammatory agents;
combinations of anti-infective and anti-inflammatory agents;
decongestants; anti-glaucoma agents, including, without limitation,
adrenergics, .beta.-adrenergic blocking agents, .alpha.-adrenergic
agonists, parasypathomimetic agents, cholinesterase inhibitors,
carbonic anhydrase inhibitors, and prostaglandins; combinations of
anti-glaucoma agents; antioxidants; nutritional supplements; drugs
for the treatment of cystoid macular edema including, without
limitation, non-steroidal anti-inflammatory agents; drugs for the
treatment of ARMD, including, without limitation, angiogenesis
inhibitors and nutritional supplements; drugs for the treatment of
herpetic infections and CMV ocular infections; drugs for the
treatment of proliferative vitreoretinopathy including, without
limitation, antimetabolites and fibrinolytics; wound modulating
agents, including, without limitation, growth factors;
antimetabolites; neuroprotective drugs, including, without
limitation, eliprodil; and angiostatic steroids for the treatment
of diseases or conditions of the posterior segment of the eye,
including, without limitation, ARMD, CNV, retinopathies, retinitis,
uveitis, macular edema, and glaucoma. Such angiostatic steroids are
more fully disclosed in U.S. Pat. Nos. 5,679,666 and 5,770,592,
which are incorporated herein in their entirety by reference.
Preferred ones of such angiostatic steroids include
4,9(11)-Pregnadien-17.alpha.,21-diol-3,20-dione and
4,9(11)-Pregnadien-17.alpha.,21-diol-3,20-dione-21-acetate. Inner
core 26 may also comprise conventional non-active excipients to
enhance the stability, solubility, penetrability, or other
properties of the active agent or the drug core.
[0034] If inner core 26 is a tablet, it may further comprise
conventional excipients necessary for tableting, such as fillers
and lubricants. Such tablets may be produced using conventional
tableting methods. The pharmaceutically active agent is preferably
distributed evenly throughout the tablet. In addition to
conventional tablets, inner core 26 may comprise a special tablet
that bioerodes at a controlled rate, releasing the pharmaceutically
active agent. By way of example, such bioerosion may occur through
hydrolosis or enzymatic cleavage. If inner core 26 is a hydrogel,
the hydrogel may bioerode at a controlled rate, releasing the
pharmaceutically active agent. Alternatively, the hydrogel may be
non-bioerodable but allow diffusion of the pharmaceutically active
agent.
[0035] Device 10 may be made by conventional polymer processing
methods, including, but not limited to, injection molding,
extrusion molding, transfer molding, and compression molding.
Preferably, device 10 is formed using conventional injection
molding techniques. Inner core 26 is preferably disposed in well 22
after the formation of body 12 of device 10. Retaining member 28 is
preferably resilient enough to allow inner core 26 to be inserted
through opening 24 and then to return to its position as shown in
FIG. 1.
[0036] Device 10 is preferably surgically placed proximate a target
tissue. The surgeon first makes an incision proximate the target
tissue. Next, the surgeon performs a blunt dissection to a level at
or near the target tissue. Once the target tissue is located, the
surgeon uses forceps to hold device 10 with internal surface 14
facing the target tissue and distal end 20 away from the surgeon.
The surgeon then introduces device 10 into the dissection tunnel,
and positions device 10 with internal surface 14 facing the target
tissue. Once in place, the surgeon may or may not use sutures to
fix device 10 to the underlying tissue, depending on the specific
tissue. After placement, the surgeon sutures the opening and places
a strip of antibiotic ointment on the surgical wound.
[0037] The physical shape of body 12, including the geometry of
internal surface 14, well 22, opening 24, and retaining member 28,
facilitate the unidirectional delivery of a pharmaceutically
effective amount of the pharmaceutically active agent from inner
core 26 to the target tissue. In particular, the absence of a
polymer layer or membrane between inner core 26 and the underlying
tissue greatly enhances and simplifies the delivery of an active
agent to the target tissue.
[0038] Device 10 can be used to deliver a pharmaceutically
effective amount of a pharmaceutically active agent to target
tissue for many years, depending on the particular physicochemical
properties of the pharmaceutically active agent employed. Important
physicochemical properties include hydrophobicity, solubility,
dissolution rate, diffusion coefficient, and tissue affinity. After
inner core 26 no longer contains active agent, a surgeon may easily
remove device 10. In addition, the "preformed" tunnel facilitates
the replacement of an old device 10 with a new device 10.
[0039] FIGS. 3 through 6B schematically illustrate an ophthalmic
drug delivery device 50 according to a preferred embodiment of the
present invention. Device 50 may be used in any case where
localized delivery of a pharmaceutically active agent to the eye is
required. Device 50 is particularly useful for localized delivery
of active agents to the posterior segment of the eye. A preferred
use for device 50 is the delivery of pharmaceutically active agents
to the retina proximate the macula for treating ARMD, choroidial
neovascularization (CNV), retinopathies, retinitis, uveitis,
macular edema, and glaucoma. Of course, device 50 may also be
utilized for localized delivery of pharmaceutically active agents
to body tissue other than the eye, if desired.
[0040] Referring first to FIG. 3, a human eye 52 is schematically
illustrated. Eye 52 has a cornea 54, a lens 56, a sclera 58, a
choroid 60, a retina 62, and an optic nerve 64. An anterior segment
66 of eye 52 generally includes the portions of eye 52 anterior of
a line 67. A posterior segment 68 of eye 52 generally includes the
portions of eye 52 posterior of line 67. Retina 62 is physically
attached to choroid 60 in a circumferential manner proximate pars
plana 70. Retina 62 has a macula 72 located slightly lateral to its
optic disk. As is well known in the ophthahnic art, macula 72 is
comprised primarily of retinal cones and is the region of maximum
visual acuity in retina 62. A Tenon's capsule or Tenon's membrane
74 is disposed on sclera 58. A conjunctiva 76 covers a short area
of the globe of eye 52 posterior to limbus 77 (the bulbar
conjunctiva) and folds up (the upper cul-de-sac) or down (the lower
cul-de-sac) to cover the inner areas of upper eyelid 78 and lower
eyelid 79, respectively. Conjunctiva 76 is disposed on top of
Tenon's capsule 74. As is shown in FIGS. 3 and 4, and as is
described in greater detail hereinbelow, device 50 is preferably
disposed directly on the outer surface of sclera 58, below Tenon's
capsule 74 for treatment of most posterior segment diseases or
conditions. In addition, for treatment of ARMD in humans, device 50
is preferably disposed directly on the outer surface of sclera 58,
below Tenon's capsule 74, with an inner core of device 50 proximate
macula 72.
[0041] FIGS. 5, 6A, and 6B schematically illustrate drug delivery
device 50 in greater detail. Device 50 generally includes a body 80
having a scleral surface 82 and an orbital surface 84. Scleral
surface 82 is preferably designed with a radius of curvature that
facilitates direct contact with sclera 58. Orbital surface 84 is
preferably designed with a radius of curvature that facilitates
implantation under Tenon's capsule 74. Body 80 preferably has a
curved, generally rectangular three-dimensional geometry with
rounded sides 86 and 88, proximal end 90, and distal end 92. As
shown best in the side sectional view of FIG. 6A, orbital surface
84 preferably has tapered surfaces 94 and 96 proximate proximal end
90 and distal end 92, respectively, that facilitate sub-Tenon
implantation of device 50 and enhance the comfort of the patient.
Body 80 may alternatively have a geometry similar to that of device
10a shown in FIG. 2. In addition, body 80 may have any other
geometry that has a curved scleral surface 82 for contact with
sclera 58. By way of example, body 80 may have a generally
cylindrical, oval, square, or other polygonal three-dimensional
geometry.
[0042] Body 80 includes a well or cavity 102 having an opening 104
to scleral surface 82. An inner core 106 is preferably disposed in
well 102. Inner core 106 is preferably a tablet comprising one or
more pharmaceutically active agents. Alternatively, inner core 106
may comprise a conventional hydrogel having one or more
pharmaceutically active agents disposed therein. A retaining member
108 is preferably disposed proximate opening 104. Retaining member
108 prevents inner core 106 from falling out of well 102. When
inner core 106 is a cylindrical tablet, retaining member 108 is
preferably a continuous rim or lip disposed circumferentially
around opening 104 having a diameter slightly less than the
diameter of tablet 106. Alternatively, retaining member 108 may
comprise one or more members that extend from body 80 into opening
104. Although not shown in FIG. 6A, inner core 106 may
alternatively comprise a suspension, solution, powder, or
combination thereof containing one or more pharmaceutically active
agents. In this embodiment, scleral surface 82 is formed without
opening 104, and the suspension, solution, powder, or combination
thereof diffuses through the relatively thin portion of scleral
surface 82 below inner core 26. Still further in the alternative,
device 50 may be formed without well 102 or inner core 106, and the
pharmaceutically active agent(s) in the form of a suspension,
solution, powder, or combination thereof may be dispersed
throughout body 80 of device 50. In this embodiment, the
pharmaceutically active agent diffuses through body 80 into the
target tissue.
[0043] The geometry and dimensions of device 50 maximize
communication between the pharmaceutically active agent of inner
core 106 and the tissue underlying scleral surface 82. Scleral
surface 82 preferably physically contacts the outer surface of
sclera 58. Although not shown in FIG. 6A or 6B, inner core 106 may
be formed so that surface 106a physically contacts the outer
surface of sclera 58. Alternatively, scleral surface 82 may be
disposed proximate the outer surface of sclera 58. By way of
example, device 50 may be disposed in the periocular tissues just
above the outer surface of sclera 58 or intra-lamellarly within
sclera 58.
[0044] Body 80 preferably comprises a biocompatible,
non-bioerodable material. Body 80 more preferably comprises a
biocompatible, non-bioerodable polymeric composition. The polymeric
composition comprising body 80, and the polymers suitable for use
in the polymeric compositions of body 80, may be any of the
compositions and polymers described hereinabove for body 12 of
device 10. Body 80 most preferably is made from a polymeric
composition comprising silicone. Body 80 is preferably impermeable
to the pharmaceutically active agent of inner core 106. When body
80 is made from a generally elastic polymeric composition, the
diameter of well 102 may be slightly less than the diameter of
inner core 106. This frictional fit secures inner core 106 within
well 102. In this embodiment, body 80 may be formed without
retaining member 108, if desired.
[0045] Inner core 106 may comprise any ophthalmically acceptable
pharmaceutically active agents suitable for localized delivery.
Exemplary pharmaceutically active agents include the
pharmaceutically active agents listed hereinabove for inner core 26
of device 10. Inner core 106 may also comprise conventional
non-active excipients to enhance the stability, solubility,
penetrability, or other properties of the active agent.
[0046] If inner core 106 is a tablet, it may further comprise
conventional excipients necessary for tableting, such as fillers
and lubricants. Such tablets may be produced using conventional
tableting methods. The pharmaceutically active agent is preferably
distributed evenly throughout the tablet. In addition to
conventional tablets, inner core 106 may comprise a special tablet
that bioerodes at a controlled rate, releasing the pharmaceutically
active agent. By way of example, such bioerosion may occur through
hydrolosis or enzymatic cleavage. If inner core 106 is a hydrogel,
the hydrogel may bioerode at a controlled rate, releasing the
pharmaceutically active agent. Alternatively, the hydrogel may be
non-bioerodable but allow diffusion of the pharmaceutically active
agent.
[0047] Device 50 may be made by conventional polymer processing
methods, including, but not limited to, injection molding,
extrusion molding, transfer molding, and compression molding.
Preferably, device 50 is formed using conventional injection
molding techniques as described hereinabove for device 10.
[0048] Device 50 is preferably surgically placed directly on the
outer surface of sclera 58 below Tenon's capsule 74 using a simple
surgical technique that is capable of being performed in an
outpatient setting. The surgeon first performs a peritomy in one of
the quadrants of eye 52. Preferably, the surgeon performs the
peritomy in the infra-temporal quadrant, about 3 mm posterior to
limbus 77 of eye 52. Once this incision is made, the surgeon
performs a blunt dissection to separate Tenon's capsule 74 from
sclera 58, forming an antero-posterior tunnel. Once the tunnel is
formed, the surgeon uses forceps to hold device 50 with scleral
surface 82 facing sclera 58 and distal end 92 away from the
surgeon. The surgeon then introduces device 50 into the tunnel in a
generally circular motion to position inner core 106 of device 50
generally above the desired portion of retina 62. The surgeon then
closes the peritomy by suturing Tenon's capsule 74 and conjunctiva
76 to sclera 58. After closing, the surgeon places a strip of
antibiotic ointment on the surgical wound. Alternatively, the
surgeon may suture proximal end 90 of device 50 to sclera 58 to
hold device 50 in the desired location before closure of the
tunnel.
[0049] In the case of ARMD in the human eye, the surgeon utilizes
the above-described technique to position inner core 106 of device
50 in one of two preferred locations in the infra-temporal quadrant
of eye 52. One preferred location is directly on the outer surface
of sclera 58, below Tenon's capsule 74, with inner core 106
positioned proximate to, but not directly above, macula 72. A
surgeon may position inner core 106 of device 50 at this location
by moving distal end 92 of device 50 below the inferior oblique
muscle in a direction generally parallel to the lateral rectus
muscle. A second preferred location is directly on the outer
surface of sclera 58, below Tenon's capsule 74, with inner core 106
positioned directly above macula 72. A surgeon may position inner
core 106 of device 50 at this location by moving distal end 92 of
device 50 toward macula 72 along a path generally between the
lateral and inferior rectus muscles and below the inferior oblique
muscle. For ARMD, the pharmaceutically active agent of inner core
106 is preferably one of the angiostatic steroids disclosed in U.S.
Pat. Nos. 5,679,666 and 5,770,592.
[0050] The physical shape of body 80 of device 50, including the
geometry of scleral surface 82, well 102, opening 104, and
retaining member 108, facilitate the unidirectional delivery of a
pharmaceutically effective amount of the pharmaceutically active
agent from inner core 106 through sclera 58, choroid 60, and into
retina 62. In particular, the absence of a polymer layer or
membrane between inner core 106 and sclera 58 greatly enhances and
simplifies the delivery of an active agent to retina 62.
[0051] It is believed that device 50 can be used to deliver a
pharmaceutically effective amount of a pharmaceutically active
agent to retina 62 for many years, depending on the particular
physicochemical properties of the pharmaceutically active agent
employed. Important physicochemical properties include
hydrophobicity, solubility, dissolution rate, diffusion
coefficient, and tissue affinity. After inner core 106 no longer
contains active agent, a surgeon may easily remove device 50. In
addition, the "pre-formed" tunnel facilitates the replacement of an
old device 50 with a new device 50.
[0052] The following example illustrates effective drug delivery to
a rabbit retina using a preferred embodiment and surgical technique
of the present invention, but are in no way limiting.
EXAMPLE
[0053] A device 50 was surgically implanted on the outer surface of
the sclera, below the Tenon's capsule, generally along the inferior
border of the lateral rectus muscle of the right eye of twenty (20)
New Zealand White rabbits using a procedure similar to that
described hereinabove for implantation of device 50 on sclera 58 of
eye 52. Device 50 was constructed as shown in FIGS. 5 through 6B,
with the following dimensions. Body 80 had a length 110 of about 15
mm, a width 112 of about 7.0 mm, and a maximum thickness 114 of
about 1.8 mm. Retaining member 108 had a thickness 116 of about
0.15 mm. Scleral surface 82 had a radius of curvature of about 8.5
mm and an arc length of about 18 mm. Inner core 106 was a
cylindrical tablet with a diameter of about 5.0 mm and a thickness
of about 1.5 mm. Opening 104 had a diameter of about 3.8 mm. Well
102 had a diameter of about 4.4 mm. The pharmaceutically active
agent used in tablet 106 was
4,9(11)-Pregnadien-17.alpha.,21-diol-3,20-di- one, an angiostatic
steroid sold by Steraloids, Inc. of Wilton, N.H., and which is more
fully disclosed in U.S. Pat. Nos. 5,770,592 and 5,679,666. The
formulation of tablet 106 consisted of 99.75 weight percent
4,9(11)-Pregnadien-17.alpha.,21-diol-3,20-dione, and 0.25 weight
percent magnesium stearate.
[0054] At one week after implantation, 4 rabbits were euthanized
and their right eyes were enucleated. The device 50 was removed
from the eyes, and the location of tablet 106 was marked on their
sclerae. Following the removal of the anterior segment and the
vitreous of each eye and inversion of the thus formed eye-cup, a 10
mm diameter circular zone of retinal tissue, concentric with and
below the location of tablet 106 on the sclera, was harvested (the
"target site"). A 10 mm diameter circular zone of retinal tissue
was also harvested from a second site located remote from the
target site and on the other side of the optic nerve. In addition,
a 10 mm diameter circular zone of retinal tissue was harvested from
a third site located between the second site and the target site.
Similar 10 mm diameter circular zones of choroidal tissue were also
harvested at the target site, second site, and third site. All
these tissues were separately homogenized, and the concentration of
angiostatic steroid in each of these tissues was determined via an
ocular pharmacokinetic study using high performance liquid
chromatography and mass spectrometry analysis (LC-MS/MS). This
procedure was repeated at 3, 6, 9, and 12 weeks after
implantation.
[0055] FIG. 7 shows the mean concentration of
4,9(11)-Pregnadien-17.alpha.- ,21-diol-3,20-dione in the retina and
the choroid at the target site as a function of time. The "error
bars" surrounding each data point represent standard deviation. As
shown in FIG. 7, device 50 delivered a pharmaceutically effective
and generally constant amount of
4,9(11)-Pregnadien-17.alpha.,21-diol-3,20-dione to the retina and
the choroid at the target site for a time period of up to twelve
weeks. In contrast, the levels of
4,9(11)-Pregnadien-17.alpha.,21-diol-3,20-dione in the retina and
the choroid at the second and third sites were at or near zero.
Therefore, device 50 also delivered a localized dose of angiostatic
steroid to the retina and the choroid at the target site.
[0056] From the above, it may be appreciated that the present
invention provides improved devices and methods for safe,
effective, rate-controlled, localized delivery of a variety of
pharmaceutically active agents to any body tissue. The surgical
procedure for implanting such devices is safe, simple, quick, and
capable of being performed in an outpatient setting. Such devices
are easy and economical to manufacture. Furthermore, because of
their capability to deliver a wide variety of pharmaceutically
active agents, such devices are useful in clinical studies to
deliver various agents that create a specific physical condition in
a patient or animal subject. In the particular field of ophthalmic
drug delivery, such devices are especially useful for localized
delivery of pharmaceutically active agents to the posterior segment
of the eye to combat ARMD, CNV, retinopathies, retinitis, uveitis,
macular edema, and glaucoma.
[0057] It is believed that the operation and construction of the
present invention will be apparent from the foregoing description.
While the apparatus and methods shown or described above have been
characterized as being preferred, various changes and modifications
may be made therein without departing from the spirit and scope of
the invention as defined in the following claims.
* * * * *