U.S. patent application number 12/856198 was filed with the patent office on 2010-12-02 for preparation of injectable suspensions having improved injectability.
This patent application is currently assigned to Alkermes Controlled Therapeutics, Inc.. Invention is credited to Joyce M. Hotz, Olufunmi L. Johnson, J. Michael Ramstack, M. Gary I. Riley, Stephen E. Zale.
Application Number | 20100303900 12/856198 |
Document ID | / |
Family ID | 24310496 |
Filed Date | 2010-12-02 |
United States Patent
Application |
20100303900 |
Kind Code |
A1 |
Ramstack; J. Michael ; et
al. |
December 2, 2010 |
PREPARATION OF INJECTABLE SUSPENSIONS HAVING IMPROVED
INJECTABILITY
Abstract
Injectable compositions having improved injectability. The
injectable compositions include microparticles suspended in an
aqueous injection vehicle having a viscosity of at least 20 cp at
20.degree. C. The increased viscosity of the injection vehicle that
constitutes the fluid phase of the suspension significantly reduces
in vivo injectability failures. The injectable compositions can be
made by mixing dry microparticles with an aqueous injection vehicle
to form a suspension, and then mixing the suspension with a
viscosity enhancing agent to increase the viscosity of the fluid
phase of the suspension to the desired level for improved
injectability.
Inventors: |
Ramstack; J. Michael;
(Lunenburg, MA) ; Riley; M. Gary I.; (Boston,
MA) ; Zale; Stephen E.; (Hopkinton, MA) ;
Hotz; Joyce M.; (Cincinnati, OH) ; Johnson; Olufunmi
L.; (Cambridge, MA) |
Correspondence
Address: |
COVINGTON & BURLING, LLP;ATTN: PATENT DOCKETING
1201 PENNSYLVANIA AVENUE, N.W.
WASHINGTON
DC
20004-2401
US
|
Assignee: |
Alkermes Controlled Therapeutics,
Inc.
Waltham
MA
|
Family ID: |
24310496 |
Appl. No.: |
12/856198 |
Filed: |
August 13, 2010 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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11826994 |
Jul 19, 2007 |
7799345 |
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12856198 |
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10681142 |
Oct 9, 2003 |
7371406 |
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11826994 |
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10259949 |
Sep 30, 2002 |
6667061 |
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10681142 |
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09577875 |
May 25, 2000 |
6495164 |
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10259949 |
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Current U.S.
Class: |
424/451 ;
514/259.41 |
Current CPC
Class: |
A61K 9/1647 20130101;
A61K 9/1641 20130101; A61K 9/1658 20130101; A61K 47/26 20130101;
A61K 9/0019 20130101; A61K 47/38 20130101; A61K 31/505 20130101;
A61K 47/34 20130101; A61P 25/18 20180101 |
Class at
Publication: |
424/451 ;
514/259.41 |
International
Class: |
A61K 9/50 20060101
A61K009/50; A61K 31/519 20060101 A61K031/519; A61P 25/18 20060101
A61P025/18 |
Claims
1. A composition suitable for injection through a needle into a
host, comprising: microparticles comprising a polymeric binder and
an active agent encapsulated within the polymeric binder, the
microparticles having a mass median diameter of at least about 10
.mu.m; and an injection vehicle, wherein the microparticles are
suspended in the injection vehicle at a concentration of greater
than about 30 mg/ml to form a suspension, wherein a fluid phase of
the suspension has a viscosity greater than about 20 cp and less
than about 600 cp at 20.degree. C., wherein the viscosity of the
fluid phase of the suspension provides injectability of the
composition through a needle into a host, wherein the polymeric
binder is selected from the group consisting of poly(glycolic
acid), poly-d,l-lactic acid; poly-l-lactic acid, copolymers of the
foregoing, poly(aliphatic carboxylic acids), copolyoxalates,
polycaprolactone, polydioxanone, poly(ortho carbonates),
poly(acetals), poly(lactic acid-caprolactone), polyorthoesters,
poly(glycolic acid-caprolactone), polyanhydrides, polyphosphazines,
albumin, and casein, wherein the injection vehicle comprises a
viscosity enhancing agent comprising sodium carboxymethyl
cellulose; a wetting agent selected from the group consisting of
polysorbate 20, polysorbate 40, and polysorbate 80; and a tonicity
adjusting agent comprising sodium chloride, and wherein the
viscosity of the fluid phase of the suspension provides
injectability of the composition into a host through a needle of
medically acceptable size.
2. The composition of claim 1, wherein the active agent is selected
from the group consisting of risperidone, 9-hydroxyrisperidone, and
pharmaceutically acceptable salts thereof.
3. The composition of claim 1, wherein the polymeric binder is
poly(d,l-lactide-co-glycolide) having a molar ratio of lactide to
glycolide in the range of from about 85:15 to about 50:50.
4. The composition of claim 1, wherein the microparticles are
suspended in the injection vehicle at a concentration of from about
100 mg/ml to about 400 mg/ml.
5. The composition of claim 1, wherein the viscosity of the fluid
phase of the suspension provides injectability of the composition
into the host through a needle ranging in diameter from 18-22
gauge.
6. The composition of claim 1, wherein the injection vehicle is
aqueous.
7. A method of making a composition suitable for injection through
a needle into a host, comprising: (a) providing microparticles
comprising a polymeric binder and an active agent encapsulated
within the polymeric binder, the microparticles having a mass
median diameter of at least about 10 .mu.m; (b) providing an
injection vehicle having a viscosity of at least 20 cp at
20.degree. C.; and (c) suspending the microparticles in the
injection vehicle at a concentration of greater than about 30 mg/ml
to form a suspension, wherein the viscosity of a fluid phase of the
suspension is in the range of from about 20 cp to about 600 cp at
20.degree. C., wherein the viscosity of the fluid phase of the
suspension provides injectability of the composition into a host
through a needle of medically acceptable size, wherein the
polymeric binder is selected from the group consisting of
poly(glycolic acid), poly-d,l-lactic acid; poly-l-lactic acid,
copolymers of the foregoing, poly(aliphatic carboxylic acids),
copolyoxalates, polycaprolactone, polydioxanone, poly(ortho
carbonates), poly(acetals), poly(lactic acid-caprolactone),
polyorthoesters, poly(glycolic acid-caprolactone), polyanhydrides,
polyphosphazines, albumin, and casein, and wherein the viscosity
enhancing agent comprises sodium carboxymethyl cellulose.
8. The method of claim 7, wherein the active agent is selected from
the group consisting of risperidone, 9-hydroxyrisperidone, and
pharmaceutically acceptable salts thereof.
9. The method of claim 7, wherein the polymeric binder is
poly(d,l-lactide-co-glycolide) having a molar ratio of lactide to
glycolide in the range of from about 85:15 to about 50:50.
10. The method of claim 7, wherein the viscosity of the fluid phase
of the suspension provides injectability of the composition into
the host through a needle ranging in diameter from 18-22 gauge.
11. The method of claim 7, wherein the microparticles are suspended
in the injection vehicle at a concentration of from about 100 mg/ml
to about 400 mg/ml.
12. The method of claim 7, wherein the injection vehicle is
aqueous.
Description
BACKGROUND OF THE INVENTION
[0001] 1. Field of the Invention
[0002] The present invention relates to preparation of injectable
compositions. More particularly, the present invention relates to
injectable suspensions having improved injectability, and to
methods for the preparation of such injectable suspensions.
[0003] 2. Related Art
[0004] Injectable suspensions are heterogeneous systems that
typically consist of a solid phase dispersed in a liquid phase, the
liquid phase being aqueous or nonaqueous. To be effective and
pharmaceutically acceptable, injectable suspensions should
preferably be: sterile; stable; resuspendable; syringeable;
injectable; isotonic; and nonirritating. The foregoing
characteristics result in manufacturing, storage, and usage
requirements that make injectable suspensions one of the most
difficult dosage forms to develop.
[0005] Injectable suspensions are parenteral compositions in that
they are introduced into an organism or host by means other than
through the gastrointestinal tract. Particularly, injectable
suspensions are introduced into a host by subcutaneous (SC) or
intramuscular (IM) injection. Injectable suspensions may be
formulated as a ready-to-use injection or require a reconstitution
step prior to use. Injectable suspensions typically contain between
0.5% and 5.0% solids, with a particle size of less than 5 .mu.m for
IM or SC administration. Parenteral suspensions are frequently
administered through needles about one-half to two inches long, 19
to 22 gauge, with an internal diameter in the range of 700 to 400
microns, respectively.
[0006] To develop an effective and pharmaceutically acceptable
injectable suspension, a number of characteristics must be
evaluated. These characteristics include syringeability,
injectability, clogging, resuspendability, and viscosity. As will
be readily apparent to one skilled in the art, other
characteristics and factors should be considered in developing an
injectable suspension (see, for example, Floyd, A. G. and Jain, S.,
Injectable Emulsions and Suspensions, Chapter 7 in Pharmaceutical
Dosage Forms: Disperse Systems Vol. 2, Edited by Lieberman, H. A.,
Rieger, M. M., and Banker, G. S., Marcel Dekker, New York (1996),
the entirety of which is incorporated herein by reference and
referred to herein as "the Floyd et al. Chapter").
[0007] Syringeability describes the ability of an injectable
suspension to pass easily through a hypodermic needle on transfer
from a vial prior to injection. It includes characteristics such as
ease of withdrawal, clogging and foaming tendencies, and accuracy
of dose measurements. As described in the Floyd et al. Chapter,
increase in the viscosity, density, particle size, and
concentration of solids in suspension hinders the syringeability of
suspensions.
[0008] Injectability refers to the performance of the suspension
during injection. Injectability includes factors such as pressure
or force required for injection, evenness of flow, aspiration
qualities, and freedom from clogging.
[0009] Clogging refers to the blockage of syringe needles while
administering a suspension. It may occur because of a single large
particle, or an aggregate that blocks the lumen of the needle due
to a bridging effect of the particles. Clogging at or near the
needle end may be caused by restrictions to flow from the
suspension. This may involve a number of factors, such as the
injection vehicle, wetting of particles, particle size and
distribution, particle shape, viscosity, and flow characteristics
of the suspension.
[0010] Resuspendability describes the ability of the suspension to
uniformly disperse with minimal shaking after it has stood for some
time. Resuspendability can be a problem for suspensions that
undergo "caking" upon standing due to settling of the deflocculated
particles. "Caking" refers to a process by which the particles
undergo growth and fusion to form a nondispersible mass of
material.
[0011] Viscosity describes the resistance that a liquid system
offers to flow when it is subjected to an applied shear stress. A
more viscous system requires greater force or stress to make it
flow at the same rate as a less viscous system. A liquid system
will exhibit either Newtonian or non-Newtonian flow based on a
linear or a non-linear increase, respectively, in the rate of shear
with the shearing stress. Structured vehicles used in suspensions
exhibit non-Newtonian flow and are typically plastic,
pseudoplastic, or shear-thinning with some thixotropy (exhibiting a
decrease in viscosity with an increase in the rate of shear).
[0012] In design of injection vehicles, viscosity enhancers are
added in order to retard settling of the particles in the vial and
syringe. However, viscosity is typically kept low, in order to
facilitate mixing, resuspension of the particles with the vehicle,
and to make the suspension easier to inject (i.e., low force on the
syringe plunger). For example, Lupron Depot from TAP
Pharmaceuticals (mean particle size of approximately 8 .mu.m)
utilizes an injection vehicle with a viscosity of approximately 5.4
cp. The fluid phase of a suspension of Decapeptyl from DebioPharm
(mean particle size of approximately 40 .mu.m), when prepared as
directed, has a viscosity of approximately 19.7 cp. Conventional
parenteral suspensions are dilute, with limitations for viscosity
because of syringeability and injectability constraints. See, for
example, the Floyd, et al. Chapter noted above.
[0013] Injectable compositions containing microparticle
preparations are particularly susceptible to injectability
problems. Microparticle suspensions may contain 10-15% solids, as
compared with 0.5-5% solids in other types of injectable
suspensions. Microparticles, particularly controlled release
microparticles containing an active agent or other type of
substance to be released, range in size up to about 250 .mu.m, as
compared with a particle size of less than 5 .mu.m recommended for
IM or SC administration. The higher concentration of solids, as
well as the larger solid particle size, make it more difficult to
successfully inject microparticle suspensions. This is particularly
true since it is also desired to inject the microparticle
suspensions using as small a needle as possible to minimize patient
discomfort.
[0014] Thus, there is a need in the art for an injectable
composition with improved injectability. There is a particular need
in the art for an injectable composition that solves the
injectability problems associated with microparticle suspensions.
The present invention, the description of which is fully set forth
below, solves the need in the art for such injectable
compositions.
SUMMARY OF THE INVENTION
[0015] The present invention relates to injectable compositions
having improved injectability, and to methods for the preparation
of such injectable compositions. In one aspect of the invention, a
composition suitable for injection through a needle into a host is
provided. The composition comprises microparticles having a
polymeric binder, with a mass median diameter of at least about 10
.mu.m. The composition also includes an aqueous injection vehicle
(the injection vehicle not being the aqueous injection vehicle that
consists of 3% by volume sodium carboxymethyl cellulose, 1% by
volume polysorbate 20, 0.9% by volume sodium chloride, and a
remaining percentage by volume of water). The microparticles are
suspended in the injection vehicle at a concentration of greater
than about 30 mg/ml to form a suspension, the fluid phase of the
suspension having a viscosity of at least 20 cp at 20.degree. C. In
other embodiments, the fluid phase of the suspension has a
viscosity at 20.degree. C. of at least about 30 cp, 40 cp, 50 cp,
and 60 cp. The composition may also comprise a viscosity enhancing
agent, a density enhancing agent, a tonicity enhancing agent,
and/or a wetting agent. The composition can be administered to a
host by injection.
[0016] In another aspect of the present invention, a method of
making a composition suitable for injection through a needle into a
host is provided. The method comprises: [0017] (a) providing
microparticles comprising a polymeric binder, said microparticles
having a mass median diameter of at least about 10 .mu.m; [0018]
(b) providing an aqueous injection vehicle having a viscosity of at
least 20 cp at 20.degree. C., wherein said injection vehicle is not
the aqueous vehicle consisting of 3% by volume sodium carboxymethyl
cellulose, 1% by volume polysorbate 20, 0.9% by volume sodium
chloride, and a remaining percentage by volume of water; and [0019]
(c) suspending the microparticles in the aqueous injection vehicle
at a concentration of greater than about 30 mg/ml to form a
suspension.
[0020] In a further aspect of the present invention, another method
for preparing a composition suitable for injection through a needle
into a host is provided. In such a method, dry microparticles are
mixed with an aqueous injection vehicle to form a first suspension.
The first suspension is mixed with a viscosity enhancing agent to
form a second suspension. The viscosity enhancing agent increases
the viscosity of the fluid phase of the second suspension. The
first suspension may be withdrawn into a first syringe, prior to
mixing with the viscosity enhancing agent. The first suspension may
be mixed with the viscosity enhancing agent by coupling the first
syringe containing the first suspension to a second syringe that
contains the viscosity enhancing agent. The first suspension and
the viscosity enhancing agent are then repeatedly passed between
the first and second syringes.
[0021] In yet a further aspect of the present invention, a method
for administering a composition to a host is provided. The method
comprises: [0022] (a) mixing dry microparticles with an aqueous
injection vehicle to form a first suspension; [0023] (b) mixing the
first suspension with a viscosity enhancing agent to form a second
suspension, wherein the viscosity enhancing agent increases the
viscosity of the fluid phase of the second suspension; and [0024]
(c) injecting the second suspension into the host.
[0025] In still a further aspect of the present invention, another
method for administering a composition to a host is provided. The
method comprises: [0026] (a) mixing dry microparticles with an
aqueous injection vehicle to form a suspension, wherein the aqueous
injection vehicle has a viscosity at 20.degree. C. of less than
about 60 cp; [0027] (b) changing the viscosity of the fluid phase
of the suspension; [0028] (c) withdrawing the suspension into a
syringe; and [0029] (d) injecting the suspension from the syringe
into the host. In a further aspect of the invention, step (b) is
carried out by changing the temperature of to the fluid phase of
the suspension. In another aspect, step (c) is performed prior to
step (b). Step (b) may be carried out by adding a viscosity
enhancing agent to the suspension in the syringe to thereby
increase the viscosity of the fluid phase of the suspension. [0030]
In still a further aspect of the invention, a method for preparing
a composition suitable for injection through a needle into a host
is provided. The method comprises: [0031] (a) mixing dry
microparticles with an aqueous injection vehicle that comprises a
viscosity enhancing agent to form a suspension; [0032] (b) removing
water from the suspension; and [0033] (c) reconstituting the
suspension with a quantity of sterile water for injection to form
an injectable suspension, wherein the quantity of sterile water for
injection is sufficient to achieve a viscosity of a fluid phase of
the injectable suspension that provides injectability of the
composition through a needle ranging in diameter from 18-22
gauge.
Features and Advantages
[0034] A feature of the present invention is that the injectable
compositions can be used to inject varying types of microparticles,
and varying types of active agents or other substances, into a
host.
[0035] A further feature of the present invention is that it allows
microparticles to be wetted to achieve a homogeneous suspension,
while improving injectability into a host and reducing in vivo
injectability failures.
[0036] The present invention advantageously provides medically
acceptable injectability rates for high concentration suspensions,
and for suspensions having large particle size.
[0037] The present invention also advantageously provides an
efficient method of improving in vivo injectability without
introducing microbial contamination or compromising aseptic
conditions.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
Overview
[0038] The present invention relates to injectable compositions
having improved injectability, and to methods for the preparation
of such injectable compositions. The injectable compositions of the
present invention overcome injectability problems, particularly
injectability failures that occur upon injection into muscle or
subcutaneous tissue. Such injectability failures will be referred
to herein as "in vivo injectability failures." In vivo
injectability failures often manifest themselves in the form of a
plug at the tip of the needle, and occur immediately or shortly
after injection has been initiated. In vivo injectability failures
are typically not predicted by laboratory or other in vitro
testing.
[0039] The inventors have unexpectedly discovered that
injectability is improved, and in vivo injectability failures
significantly and unexpectedly reduced, by increasing the viscosity
of the fluid phase of an injectable suspension. This is in contrast
to conventional teachings that an increase in the viscosity hinders
injectability and syringeability.
[0040] Viscous vehicles, however, are not optimal for preparing
homogeneous suspensions of microparticles because of the relative
inability of viscous vehicles to penetrate and wet out a mass of
dry particles. Suspensions prepared with viscous vehicles are prone
to clump irreversibly. Consequently, such suspensions are not
injectable via needles of medically acceptable size. A further
disadvantage of viscous suspensions is the lack of ease of
transferring such suspensions from the vial or container used to
prepare the suspension to the syringe used for injection.
[0041] The present invention also solves the additional problems
that arise from use of a viscous injection vehicle. In accordance
with the present invention, microparticles are suspended in an
injection vehicle having suitable wetting characteristics. The
viscosity of the fluid phase of the injectable suspension is
increased prior to injecting the suspension in order to improve
injectability, and to reduce in vivo injectability failures.
[0042] To ensure clarity of the description that follows, the
following definitions are provided. By "microparticles" or
"microspheres" is meant particles that contain an active agent or
other substance dispersed or dissolved within a polymer that serves
as a matrix or binder of the particle. The polymer is preferably
biodegradable and biocompatible. By "biodegradable" is meant a
material that should degrade by bodily processes to products
readily disposable by the body and should not accumulate in the
body. The products of the biodegradation should also be
biocompatible with the body. By "biocompatible" is meant not toxic
to the body, is pharmaceutically acceptable, is not carcinogenic,
and does not significantly induce inflammation in body tissues. As
used herein, "body" preferably refers to the human body, but it
should be understood that body can also refer to a non-human animal
body. By "weight %" or "% by weight" is meant parts by weight per
hundred parts total weight of microparticle. For example, 10 wt. %
active agent would mean 10 parts active agent by weight and 90
parts polymer by weight. Unless otherwise indicated to the
contrary, percentages (%) reported herein are by volume. By
"controlled release microparticle" or "sustained release
microparticle" is meant a microparticle from which an active agent
or other type of substance is released as a function of time. By
"mass median diameter" is meant the diameter at which half of the
distribution (volume percent) has a larger diameter and half has a
smaller diameter.
METHOD AND EXAMPLES
[0043] The following examples are provided to explain the
invention, and to describe the materials and methods used in
carrying out the invention. The examples are not intended to limit
the invention in any manner.
Example 1
In vitro Sieve Test Study
[0044] To evaluate in vivo injectability failures, an in vitro
sieve test study was conducted to assess and predict in vivo
injectability, and to determine the key factors affecting
injectability. The following factors were investigated during the
in vitro sieve test study: injection vehicle formulation;
microparticle morphology; needle diameter; suspension
concentration; and particle size as exhibited by sieve screen size
used to screen the microparticles during the manufacturing
process.
[0045] Three batches of risperidone microparticles were
manufactured at a 125 gm scale using a process substantially the
same as that disclosed in U.S. Pat. No. 5,792,477, the entirety of
which is incorporated herein by reference (see, for example,
Example 1 in U.S. Pat. No. 5,792,477). Three batches of risperidone
microparticles were manufactured at a 1 Kg scale using the process
described below in Example 7. All batches had similar particle
sizes (ranging from a Mass Median Diameter of 91 .mu.m to 121
.mu.m) based on Hyac-Royco analysis of representative bulk material
sieved through a 180 .mu.m sieve screen. A 160 mg or 320 mg
quantity of the microparticles (equivalent to a 50 or 100 mg dose
of the risperidone active agent) was transferred, using a manual
Perry powder filler with a 5/16 inch ID barrel, into a 5 cc glass
vial, and capped with a Teflon lined septum.
[0046] Two injection vehicles were used in the in vitro sieve test
study. The first injection vehicle ("Formula 1") was an aqueous
vehicle consisting of 1.5% by volume carboxymethyl cellulose (CMC),
30% by volume sorbitol, and 0.2% by volume Tween 20 (polysorbate
20). The viscosity of the first injection vehicle was approximately
27 cp at 20.degree. C. The second injection vehicle ("Formula 2")
was an aqueous vehicle consisting of 0.75% by volume CMC, 15% by
volume sorbitol, and 0.2% by volume Tween 20 (polysorbate 20). The
viscosity of the second injection vehicle was approximately 7 cp at
20.degree. C.
[0047] The microparticle suspension was prepared as follows. The
injection vehicle was aspirated into a 5 cc syringe through a
needle. The vehicle was then injected into the glass vial
containing the microparticles, and the needle was removed. The
glass vial was then rolled between the palms until the
microparticles were completely suspended, approximately one minute.
The needle was reinserted into the vial so that the bevel of the
needle was just through the septum with the opening facing toward
the vial bottom. The vial was inverted and the suspension was
withdrawn. The syringe was rotated 180.degree. around its axis, and
the remaining suspension was aspirated into the syringe.
[0048] Sieve screens with mesh opening sizes of 180, 212, 250, 300,
355, and 425 .mu.m were used. The bevel of the syringe needle was
placed on the mesh of the sieve screen so that the bevel was in
full contact with the mesh. The needle was oriented so the opening
of the needle was flush against the mesh of the screen. This
prevented the mesh from entering the bevel, while maintaining the
required restrictive area. The suspension was tried on the smallest
sieve mesh first (highest screen resistance). If the suspension
fouled the needle on this sieve mesh, the needle was unclogged by
retracting the plunger of the syringe, depressing the plunger while
the syringe was in the upward position, and passing an aliquot of
suspension through the needle. The injection process was tried
again using the next greater mesh size, and repeated until the
suspension was successfully injected. All preparations were done in
triplicate.
[0049] A three-factor Box-Behnken statistical designed experiment
was constructed to evaluate the following independent variables:
manufacturing bulk sieve size (125, 150, and 180 .mu.m); needle ID
(19 TW, 20 RW, and 22 RW gauge-ID of 19 TW (thin wall) equivalent
to 18 RW (regular wall)); and suspension concentration (0.074,
0.096, and 0.138 w/w-corresponds to approximately 300 mg
microparticle dose diluted with 4, 3, and 2 cc, respectively, of
injection vehicle).
The following scoring system was used:
TABLE-US-00001 Score Result 0 Needle Block 1 Passes through a 425
.mu.m screen 2 Passes through a 355 .mu.m screen 3 Passes through a
300 .mu.m screen 4 Passes through a 250 .mu.m screen 5 Passes
through a 212 .mu.m screen
[0050] Table 1 below shows the score obtained for screen resistance
tests using this scoring system for the 1 Kg and the 125 gm batches
for each of the injection vehicles tested.
TABLE-US-00002 TABLE 1 Mean Score Mfg Bulk Sieve Size n Formula 2
.apprxeq. 7 cp Formula 1 .apprxeq. 27 cp 1 Kg Batches <180 9 2.3
2.3 <125 9 3.4 3.7 125 Gm Batches <180 6 1.5 2.0 <150 6
3.0 2.8 <125 6 3.0 2.5
[0051] As shown in Table 1, the screen resistance tests showed no
significant difference between the two injection vehicles tested.
Variations in suspension concentration and injection vehicle
viscosity showed little to no effect. For the 1 Kg Batches, the
mean scores were identical for the <180 manufacturing bulk sieve
size, even though the viscosity of the Formula 1 injection vehicle
was approximately 27 cp, and the viscosity of the Formula 2
injection vehicle was significantly less, approximately 7 cp. The
scores for the other 1 Kg Batch and for the 125 Gm Batches varied
modestly (0.2 to 0.5) between the two injection vehicles, thereby
indicating that the injection vehicle viscosity had little effect.
The tests conducted during the in vitro sieve test study show that
in vitro injectability is strongly controlled by microparticle
morphology and size. Needle gauge had a more modest effect. As will
be discussed in more detail below, in vivo data supported the
responses of microparticle morphology, size, and suspension
concentration, but contradicted the effect of injection vehicle
viscosity. Particularly, the in vivo studies showed a dramatic
improvement in injectability with increased injection vehicle
viscosity.
In Vivo Injectability
Example 2
Pig Study
[0052] The injectability of risperidone microparticles was
evaluated in Yorkshire weanling pigs. The study revealed that the
IM injectability of risperidone microparticles is dependent upon
injection vehicle viscosity and microparticle size. Reducing the
injection vehicle viscosity led to a higher rate of injection
failures due to needle clogging.
[0053] Risperidone microparticles were manufactured at the 125 gm
scale in the same manner noted above for the in vitro sieve test
study. The microparticles were sized to <125 .mu.m and <150
.mu.m using USA Standard Testing Sieves Nos. 120 and 100,
respectively. The same two injection vehicles (Formula 1 and
Formula 2) described above for the in vitro sieve test study were
used in the pig study. 19 gauge TW.times.1.5 inch hypodermic
needles (Becton-Dickinson Precisionglide.RTM. catalog number
305187) and 3 cc hypodermic syringes (Becton-Dickinson catalog
number 309585) were used.
[0054] The injection experiments were conducted in male and female
Yorkshire weanling pigs approximately 6 weeks in age (10-15 kg).
The animals were anesthetized with low doses of Telazole and
Xylazine and with halothane if needed. Injection sites were shaved
and cleansed with betadine swabs prior to microparticle
administration.
[0055] Injections to the hind quarters were administered to the
biceps femoris in the upper hind limb. Injection sites in the legs
were to the superficial digital flexor muscles in the forelimb, and
to the cranial tibial muscle in the hindlimb.
[0056] Microparticles and injection vehicles were equilibrated to
ambient temperature for at least 30 minutes. Using a 3 ml syringe
equipped with a 1.5 inch 19 gauge thin wall needle, the prescribed
volume of injection vehicle was withdrawn into the syringe, and
injected into the vial containing the microparticles. The
microparticles were suspended in the injection vehicle by orienting
the vial horizontally and rolling it between the palms of the
operator's hands. This was done without removing the needle/syringe
from the septum. The time required to fully suspend the
microparticles was approximately one minute.
[0057] The suspended microparticles were then withdrawn into the
same needle/syringe and injected. Following insertion of the needle
and prior to injection of the suspension, the syringe plunger was
withdrawn slightly to confirm that the needle was located in the
extravascular space. The time interval between aspiration of the
suspension and injection was usually less than one minute.
Injection regions were evaluated to pinpoint the site of
microparticle deposition and to assess the distribution of
microparticles in the tissue.
[0058] Table 2 below shows the effect on injectability as a
function of injection vehicle viscosity, injection site, and
microparticle concentration. A vehicle viscosity of "high" refers
to the injection vehicle of Formula 1 described above, having a
viscosity of approximately 27 cp at 20.degree. C. Similarly, a
vehicle viscosity of "low" refers to the injection vehicle of
Formula 2 described above, having a viscosity of approximately 7 cp
at 20.degree. C. The size of the microparticles for the results
shown in Table 2 is 180 .mu.m.
TABLE-US-00003 TABLE 2 Vehicle Microparticle Viscosity Dose Volume
Site Failure rate High 160 mg 1 mL Hind quarter 0/10 High 160 mg 1
mL Leg 1/8 Low 160 mg 1 mL Hind quarter 4/7 High 320 mg 1 mL Hind
quarter 0/4
[0059] As can be seen from Table 2, increased failure rates were
observed with the lower viscosity injection vehicle (4 failures
with 7 injections), and when the injection site was in the leg (1
failure per 8 injections). The increased failure rate due to
reduced viscosity was statistically significant at the 1% level
(Fisher Exact Test).
[0060] Table 3 below summarizes injectability data for
microparticles fractionated by size. Similar trends were observed
when the system was stressed by decreasing the vehicle viscosity,
with failure rates being higher with the <180 .mu.m fraction.
The <125 .mu.m fraction and the <150 .mu.m fraction were
indistinguishable in terms of failure rate. The low viscosity data
show statistically significant differences between <180 .mu.m
fraction and <150 .mu.m fraction, and between <180 .mu.m
fraction and <125 .mu.m fraction at 1% and 3% confidence levels,
respectively (Fisher Exact Test).
TABLE-US-00004 TABLE 3 Avg. % Max. delivered particle Vehicle
Volume Failure (failed size (.mu.m) Viscosity (mL) Site rate
injections).sup.1 180 High 2.0 Leg 0/5 n/a 150 High 2.0 Leg 0/5 n/a
125 High 2.0 Leg 0/5 n/a 180 High 1.0 Leg 2/4 0 150 High 1.0 Leg
0/4 n/a 125 High 1.0 Leg 0/4 n/a 180 Low 2.0 Hind quarter 8/10 33
150 Low 2.0 Hind quarter 2/10 18 125 Low 2.0 Hind quarter 3/10 80
.sup.1Average fraction of dose delivered prior to needle clog
(failed injections only)
[0061] The in vivo pig study demonstrates a lower injectability
failure rate with a higher viscosity injection vehicle, over a
range of particle sizes. The in vitro sieve test study did not
predict the viscosity dependence observed in the pig study.
Example 3
Sheep Study
[0062] A two-part sheep study was conducted to investigate in vivo
injectability as a function of injection vehicle composition and
viscosity, and suspension concentration. In Part I, risperidone
microparticles were prepared at the 1 Kg scale using the process
described below in Example 7. A batch of placebo microparticles was
prepared using the process shown and described in U.S. Pat. No.
5,922,253, the entirety of which is incorporated herein by
reference. The two types of microparticles were studied at two
suspension concentrations of 150 and 300 mg/ml. Animal
injectability tests were conducted using 3 cc syringes and 22 gauge
TW.times.1.5 inch needles (Becton-Dickinson).
[0063] Five injection vehicles were used in Part I. The five
injection vehicles were made using one or more of the three
injection vehicle formulations shown below:
TABLE-US-00005 Vehicle A 0.9% Saline; 0.1% Tween 20 Vehicle B 1.5%
CMC; 30% Sorbitol; 0.2% Tween 20 Vehicle C 3% CMC; 0.1% Tween 20;
0.9% Saline
[0064] Animal studies were conducted using domestic sheep weighing
approximately 100-150 pounds. The animals were anesthetized with
Telazole/Xylazine/Atropine intramuscularly and further supplemented
with isofluorane gas (approximately 1-2%) during the injection
procedure. Prior to injection, the animal's dorsal, gluteal, and
upper leg regions were shaved and cleaned with alcohol. Injection
sites were visualized prior to and during dosing using ultrasound
(EI Medical).
[0065] The microparticles and injection vehicles were equilibrated
to ambient temperature prior to dose suspension. Using a 3 cc
syringe and 22 gauge thin-walled needle, the vehicle was aspirated
and injected into the microparticle vial. The risperidone
microparticles were suspended in 1 ml of vehicle at approximate
concentrations of 150 or 300 mg/ml. Placebo microparticles were
suspended in 2 or 1 ml of vehicle at approximate concentrations of
150 or 300 mg/ml. The vial was then agitated by hand for
approximately 1 minute until the microparticles were suspended. The
suspension was then aspirated back into the syringe using the same
needle. Care was taken to recover the maximum amount of suspension
from the vial. Preparation of dose suspensions was conducted
randomly by three individuals.
[0066] All doses were injected by a single individual into the
animal almost immediately after preparation. The rate of injection
was maintained constant at approximately 5-10 seconds.
[0067] The results from Part I are shown in Table 4 below.
Viscosities were determined by Brookfield Model LVT viscometer
fitted with a UL adapter. Densities were measured for Vehicles A,
B, and C. Densities for the combination vehicles made up of
Vehicles A, B, and C were determined by interpolation based upon
the ratio of Vehicles A, B, and C in the combination vehicle.
TABLE-US-00006 TABLE 4 Viscosity Density Conc Vehicle (cp) (mg/ml)
(mg/ml).sup.2 Failures Vehicle A 1.0 1.01 150 8/10 Vehicle B 24.0
1.11 150 1/10 24.0 1.11 300 0/10 Vehicle C 56.0 1.04 150 0/10 56.0
1.04 150 .sup. 1/10.sup.1 56.0 1.04 300 0/10 3 Parts Vehicle B:
11.1 1.08 300 0/5 1 Part Vehicle A 1 Part Vehicle B: 2.3 1.03 300
7/10 3 Parts Vehicle A .sup.1Placebo Microparticles. All other
results are risperidone microparticles. .sup.2mg microparticles/ml
diluent
[0068] In order to isolate the effect of injection vehicle
viscosity on injectability, additional sheep injectability tests
(Part II) were conducted. The injectability results are shown below
in Table 5. Viscosities were determined by Brookfield Model LVT
viscometer fitted with a UL adapter. In Part II, the suspension
concentration was fixed at 300 mg/ml. The tests in Part II were
carried out using risperidone microparticles prepared in the same
manner as in Part I, using the same injection protocol. The
injection vehicles included Vehicle C and Vehicle A as described
above, as well as injection vehicles prepared by diluting Vehicle C
with Vehicle A. For example, the injection vehicle formulation
having a viscosity of 22.9 cp is formulated by combining Vehicle C
and Vehicle A in a 1:1 ratio, thereby forming Diluent 1.
TABLE-US-00007 TABLE 5 Viscosity Density Conc Vehicle (cp) (mg/ml)
(mg/ml) Failures Vehicle C 63.8 1.04 300 2/10 1:1 Vehicle C:Diluent
1 37.6* 1.03 300 2/10 1:1 Vehicle C:Vehicle A 22.9 1.03 300 1/10
(Diluent 1) 1:1 Diluent 1:Vehicle A 11.3 1.02 300 5/10 (Diluent 2)
1:1 Diluent 2:Vehicle A 1.4 1.01 300 7/10 Vehicle A 1 1.01 300
10/10 *estimate, insufficient sample
[0069] The data for Parts I and II shown in Tables 4 and 5 clearly
show that the injection vehicle viscosity has an effect on
injectability. Viscosities of at least about 20 cp are necessary
for successful and medically acceptable injectability rates. At
viscosities of less than or equal to about 11 cp, in vivo
injectability failures increase significantly.
[0070] The effect of a density enhancing agent can be seen by
comparing the injectability failures using the vehicle in Table 4
having a viscosity of 11.1 cp with the vehicle in Table 5 having a
viscosity of 11.3 cp. The viscosity of these two vehicles is nearly
the same. However, the Table 4 vehicle had 0/5 failures while the
Table 5 vehicle had 5/10 failures. The Table 4 vehicle has a higher
density (1.08 mg/ml) compared to the Table 5 vehicle (1.02 mg/ml).
The Table 4 vehicle includes a density enhancing agent, sorbitol,
while the Table 5 vehicle contains no sorbitol or other density
enhancing agent.
Example 4
Ex Vivo Injectability Tests
[0071] Injectability tests were conducted with several injection
vehicles prepared at viscosities exceeding .about.50 cp. Injection
vehicles having viscosities in excess of 50 cp were mixed, using a
syringe-syringe mixing method described in more detail in Example 5
below, in which the viscosity enhancing agent was introduced after
suspending the microparticles in the 50 cp vehicle.
[0072] Subcutaneous injections of blank (placebo) PLGA
(poly(d,l-lactic-co-glycolic acid)) microparticles, having an
approximate mass median diameter of 50 .mu.m, were made into
previously harvested pig skin using four injection vehicles having
viscosities at .about.25.degree. C. of approximately 53.1 to
>1000 cp at the time of formulation. The vehicles were
subsequently autoclaved before use, and the final viscosity
(viscosity of the fluid phase of the injectable suspension) varied
between approximately 5-60% from the nominal starting viscosity
value. The most viscous injection vehicle was approximately 13
times the viscosity of the 50 cp formulation. In this ex vivo
model, increasing the viscosity of the fluid phase of the
injectable suspension decreased injection failure rate, even when
microparticle concentration was raised from 175 to 250 mg/ml, at a
needle size of 22 G. Maximal improvement in injectability, within
this range of concentration and needle size, was achieved with
injection vehicles having a viscosity of approximately 250 cp.
[0073] In another study, four injection vehicles having measured
viscosities of 53 to 251 cp were evaluated for subcutaneous
injectability in anesthetized pigs. Microparticle concentrations
were 150 and 190 mg/ml. Injection failure was directly related to
microparticle concentration, and inversely related to viscosity
level. At 53 cp, approximately 50% of injections failed, while at
higher viscosities, failures diminished. At the highest viscosity
(251 cp), zero failures were recorded at both microparticle
concentrations.
Example 5
Methods for Preparing Injectable Compositions
[0074] Methods for preparing injectable compositions in accordance
with the present invention will now be described. In accordance
with the present invention, microparticles are first mixed with an
injection vehicle having suitable viscosity and wetting
characteristics to achieve a homogeneous mono-particulate
suspension. The viscosity of the fluid phase of the suspension is
then changed, preferably increased, to achieve a viscosity that
inhibits suspension separation and clogging under conditions of
normal clinical use. In accordance with one method of the present
invention, dry microparticles are mixed with an aqueous injection
vehicle to form a first suspension. The first suspension is mixed
with a viscosity enhancing agent to form a second suspension. The
viscosity enhancing agent increases the viscosity of the fluid
phase of the second suspension. The second suspension is then
injected into a host.
[0075] One embodiment for carrying out such a method will now be
described. Vialed dry microparticles are mixed with an aqueous
injection vehicle having a viscosity less than about 60 cp at
20.degree. C., preferably about 20-50 centipoise. The concentration
of microparticles in the mixture is greater than about 30 mg/ml,
preferably about 100-400 mg microparticles/ml. The mixture is
agitated until a homogeneous suspension is formed. The homogeneous
suspension is withdrawn into a first hypodermic syringe. The first
syringe is connected to a second syringe containing a viscosity
enhancing agent. A viscosity enhancing agent suitable for use with
the present invention is sodium carboxymethyl cellulose (CMC),
preferably having a viscosity of from about 1000 to about 2000 cp
at 20.degree. C. It should be understood that the present invention
is not limited to the use of CMC as the viscosity enhancing agent,
and other suitable viscosity enhancing agents may be used. The
added volume of the viscosity enhancing agent is approximately
10-25% of the volume of the microparticle suspension.
[0076] The microparticle suspension and the viscosity enhancing
agent are mixed to form the injectable composition by repeatedly
passing the microparticle suspension and the viscosity enhancing
agent between the first and second syringes. Such a syringe-syringe
mixing method was used in the injectability tests described in
Example 4 above. After mixing with the viscosity enhancing agent,
the viscosity of the fluid phase of the microparticle suspension is
from about 200 cp to about 600 cp at 20.degree. C. A hypodermic
needle is attached to the syringe containing the injectable
composition, and the injectable composition is injected into a host
in a manner well known to one of skill in the art.
[0077] An alternate embodiment for carrying out the method of the
present invention will now be described. Dry microparticles are
mixed with an aqueous injection vehicle having a viscosity of less
than about 60 cp at 20.degree. C. to form a suspension. The
viscosity of the fluid phase of the suspension is changed in a
manner that will be described in more detail below. The suspension
that constitutes the injectable composition is withdrawn into a
syringe, and the injectable composition is injected from the
syringe into the host. Preferably, the viscosity of the fluid phase
of the suspension is changed after the suspension has been
withdrawn into the syringe.
[0078] In one aspect of this alternate embodiment, the viscosity is
changed by changing the temperature of the fluid phase of the
injectable suspension. The methods and techniques for changing the
viscosity of a liquid by changing the temperature of the liquid are
readily apparent to one skilled in the art. The temperature of the
fluid phase of the suspension is changed until the desired
viscosity of the fluid phase has been reached. The suspension now
has the desired fluid phase viscosity for injection into a host,
and constitutes the injectable composition. At this point, the
suspension is withdrawn into the syringe and injected into the
host. Alternatively, the suspension can be withdrawn into the
syringe prior to changing the temperature of the fluid phase of the
suspension to achieve the desired fluid phase viscosity. For
example, an injection vehicle that comprises a polymer solution can
be used as the viscosity of polymer solutions is
temperature-dependent. A polymer solution can be used to suspend
the microparticles under low-viscosity conditions suitable for
wetting and suspension formation. Once the microparticles are
suspended, the suspension is drawn up into a syringe. The
temperature is then changed to induce higher viscosity in the
injection vehicle constituting the fluid phase of the suspension,
and the suspension having increased viscosity is injected into a
host.
[0079] In another aspect of this alternate embodiment, the
viscosity is changed by adding a viscosity enhancing agent to the
suspension. The suspension is withdrawn into the syringe, and then
the viscosity enhancing agent is added to the suspension in the
syringe, thereby increasing the viscosity of the aqueous injection
vehicle constituting the fluid phase of the suspension. The
suspension now has the desired fluid phase viscosity for injection
into a host, and constitutes the injectable composition. The
suspension is then injected into the host. Preferably, the
viscosity enhancing agent is added to the suspension immediately
prior to injection into the host. Suitable viscosity enhancing
agents include sodium carboxymethyl cellulose, polyvinylpyrrolidone
(PVP), such as PLASDONE, available from GAF Chemicals Corp., Wayne,
N.J., and hydroxypropylmethylcellulose (HPMC), such as Methocel,
available from Dow Chemical Co., Midland, Mich. However, other
viscosity enhancing agents may be used, as would be readily
apparent to one of skill in the art.
[0080] In another embodiment of the invention, the injectable
compositions of the present invention are prepared by providing
microparticles that comprise a polymeric binder and that have a
mass median diameter of at least about 10 .mu.m. The mass median
diameter of the microparticles is preferably less than about 250
.mu.m, and more preferably, in the range of from about 20 .mu.m to
about 150 .mu.m. Such microparticles can be made in the manner
disclosed and described herein, or in any other manner known to one
skilled in the art. An aqueous injection vehicle is provided. Such
an aqueous injection vehicle can be made in the manner disclosed
and described herein, or in any other manner known to one skilled
in the art. The microparticles are suspended in the aqueous
injection vehicle at a concentration of greater than about 30 mg/ml
to form a suspension, the fluid phase of the suspension having a
viscosity of at least 20 cp at 20.degree. C.
[0081] In yet a further embodiment of the present invention, dry
microparticles are mixed with an aqueous injection vehicle
containing a viscosity enhancing agent to form a suspension.
Suitable viscosity enhancing agents include sodium carboxymethyl
cellulose, polyvinylpyrrolidone (PVP), such as PLASDONE, available
from GAF Chemicals Corp., Wayne, N.J., and
hydroxypropylmethylcellulose (HPMC), such as Methocel, available
from Dow Chemical Co., Midland, Mich. However, other viscosity
enhancing agents may be used, as would be readily apparent to one
of skill in the art. The suspension is then dispensed into vials.
The vials are lyophilized (or vacuum dried) to remove the water.
Prior to injection, the vial contents are reconstituted with
sterile water for injection in a quantity sufficient to achieve the
desired viscosity for the fluid phase of the reconstituted
injectable suspension. Preferably, the vial contents are
reconstituted with a quantity of sterile water for injection
sufficient to achieve a viscosity of a fluid phase of the
injectable suspension that provides injectability of the
composition through a needle ranging in diameter from 18-22
gauge.
Example 6
Injectable Compositions
[0082] The injectable compositions of the present invention will
now be described. The injectable compositions of the present
invention are suitable for injection through a needle into a host.
In one embodiment, the injectable compositions comprise
microparticles suspended in an aqueous injection vehicle. The
microparticles preferably have a mass median diameter of at least
about 10 .mu.m to about 250 .mu.m, preferably in the range of from
about 20 .mu.m to about 150 .mu.m. However, it should be understood
that the invention is not limited to microparticles in this size
range, and that smaller or larger microparticles may also be
used.
[0083] The microparticles preferably comprise a polymeric binder.
Suitable polymeric binder materials include poly(glycolic acid),
poly-d,l-lactic acid, poly-l-lactic acid, copolymers of the
foregoing, poly(aliphatic carboxylic acids), copolyoxalates,
polycaprolactone, polydioxanone, poly(ortho carbonates),
poly(acetals), poly(lactic acid-caprolactone), polyorthoesters,
poly(glycolic acid-caprolactone), polyanhydrides, polyphosphazines,
albumin, casein, and waxes. Poly(d,l-lactic-co-glycolic acid) is
commercially available from Alkermes, Inc. (Blue Ash, Ohio). A
suitable product commercially available from Alkermes, Inc. is a
50:50 poly(d,l-lactic-co-glycolic acid) known as MEDISORB.RTM. 5050
DL. This product has a mole percent composition of 50% lactide and
50% glycolide. Other suitable commercially available products are
MEDISORB.RTM. 6535 DL, 7525 DL, 8515 DL and poly(d,l-lactic acid)
(100 DL). Poly(lactide-co-glycolides) are also commercially
available from Boehringer Ingelheim (Germany) under its
Resomer.RTM. mark, e.g., PLGA 50:50 (Resomer.RTM. RG 502), PLGA
75:25 (Resomer.RTM. RG 752) and d,l-PLA (Resomer.RTM. RG 206), and
from Birmingham Polymers (Birmingham, Ala.). These copolymers are
available in a wide range of molecular weights and ratios of lactic
acid to glycolic acid.
[0084] One type of microparticle suitable for use with the present
invention is a sustained-release microparticle that is
biodegradable. However, it should be understood by one skilled in
the art that the present invention is not limited to biodegradable
or other types of sustained-release microparticles. As would be
apparent to one skilled in the art, the molecular weight of the
polymeric binder material for biodegradable microparticles is of
some importance. The molecular weight should be high enough to
permit the formation of satisfactory polymer coatings, i.e., the
polymer should be a good film former. Usually, a satisfactory
molecular weight is in the range of 5,000 to 500,000 daltons,
preferably about 150,000 daltons. However, since the properties of
the film are also partially dependent on the particular polymeric
binder material being used, it is very difficult to specify an
appropriate molecular weight range for all polymers. The molecular
weight of the polymer is also important from the point of view of
its influence upon the biodegradation rate of the polymer. For a
diffusional mechanism of drug release, the polymer should remain
intact until all of the drug is released from the microparticles
and then degrade. The drug can also be released from the
microparticles as the polymeric binder bioerodes. By an appropriate
selection of polymeric materials a microparticle formulation can be
made in which the resulting microparticles exhibit both diffusional
release and biodegradation release properties. This is useful in
according multiphasic release patterns.
[0085] The microparticles may include an active agent or other type
of substance that is released from the microparticles into the
host. Such active agents can include 1,2-benzazoles, more
particularly, 3-piperidinyl-substituted 1,2-benzisoxazoles and
1,2-benzisothiazoles. The most preferred active agents of this kind
are
3-[2-[4-(6-fluoro-1,2-benzisoxazol-3-yl)-1-piperidinyl]ethyl]-6,7,8,9-tet-
rahydro-2-methyl-4H-pyrido[1,2-a]pyrimidin-4-one ("risperidone")
and
3-[2-[4-(6-fluoro-1,2-benzisoxazol-3-yl)-1-piperidinyl]ethyl]-6,7,8,9-tet-
rahydro-9-hydroxy-2-methyl-4H-pyrido[1,2-a]pyrimidin-4-one
("9-hydroxyrisperidone") and the pharmaceutically acceptable salts
thereof. Risperidone (which term, as used herein, is intended to
include its pharmaceutically acceptable salts) is most preferred.
Risperidone can be prepared in accordance with the teachings of
U.S. Pat. No. 4,804,663, the entirety of which is incorporated
herein by reference. 9-hydroxyrisperidone can be prepared in
accordance with the teachings of U.S. Pat. No. 5,158,952, the
entirety of which is incorporated herein by reference.
[0086] Other biologically active agents include non-steroidal
antifertility agents; parasympathomimetic agents; psychotherapeutic
agents; tranquilizers; decongestants; sedative hypnotics; steroids;
sulfonamides; sympathomimetic agents; vaccines; vitamins;
antimalarials; anti-migraine agents; anti-Parkinson agents such as
L-dopa; anti-spasmodics; anticholinergic agents (e.g. oxybutynin);
antitussives; bronchodilators; cardiovascular agents such as
coronary vasodilators and nitroglycerin; alkaloids; analgesics;
narcotics such as codeine, dihydrocodienone, meperidine, morphine
and the like; non-narcotics such as salicylates, aspirin,
acetaminophen, d-propoxyphene and the like; opioid receptor
antagonists, such as naltrexone and naloxone; antibiotics such as
gentamycin, tetracycline and penicillins; anti-cancer agents;
anti-convulsants; anti-emetics; antihistamines; anti-inflammatory
agents such as hormonal agents, hydrocortisone, prednisolone,
prednisone, non-hormonal agents, allopurinol, indomethacin,
phenylbutazone and the like; prostaglandins and cytotoxic
drugs.
[0087] Still other suitable active agents include estrogens,
antibacterials; antifungals; antivirals; anticoagulants;
anticonvulsants; antidepressants; antihistamines; and immunological
agents.
[0088] Other examples of suitable biologically active agents
include peptides and proteins, analogs, muteins, and active
fragments thereof, such as immunoglobulins, antibodies, cytokines
(e.g. lymphokines, monokines, chemokines), blood clotting factors,
hemopoietic factors, interleukins (IL-2, IL-3, IL-4, IL-6),
interferons (.beta.-IFN, .alpha.-IFN and .gamma.-IFN),
erythropoietin, nucleases, tumor necrosis factor, colony
stimulating factors (e.g., GCSF, GM-CSF, MCSF), insulin, enzymes
(e.g., superoxide dismutase, tissue plasminogen activator), tumor
suppressors, blood proteins, hormones and hormone analogs (e.g.,
growth hormone, adrenocorticotropic hormone and luteinizing hormone
releasing hormone (LHRH)), vaccines (e.g., tumoral, bacterial and
viral antigens); somatostatin; antigens; blood coagulation factors;
growth factors (e.g., nerve growth factor, insulin-like growth
factor); protein inhibitors, protein antagonists, and protein
agonists; nucleic acids, such as antisense molecules;
oligonucleotides; and ribozymes. Small molecular weight agents
suitable for use in the invention include, antitumor agents such as
bleomycin hydrochloride, carboplatin, methotrexate and adriamycin;
antipyretic and analgesic agents; antitussives and expectorants
such as ephedrine hydrochloride, methylephedrine hydrochloride,
noscapine hydrochloride and codeine phosphate; sedatives such as
chlorpromazine hydrochloride, prochlorperazine hydrochloride and
atropine sulfate; muscle relaxants such as tubocurarine chloride;
antiepileptics such as sodium phenyloin and ethosuximide; antiulcer
agents such as metoclopramide; antidepressants such as
clomipramine; antiallergic agents such as diphenhydramine;
cardiotonics such as theophillol; antiarrhythmic agents such as
propranolol hydrochloride; vasodilators such as diltiazem
hydrochloride and bamethan sulfate; hypotensive diuretics such as
pentolinium and ecarazine hydrochloride; antidiuretic agents such
as metformin; anticoagulants such as sodium citrate and heparin;
hemostatic agents such as thrombin, menadione sodium bisulfite and
acetomenaphthone; antituberculous agents such as isoniazide and
ethanbutol; hormones such as prednisolone sodium phosphate and
methimazole.
[0089] The microparticles can be mixed by size or by type. However,
it should be understood that the present invention is not limited
to the use of biodegradable or other types of microparticles that
contain an active agent. In one embodiment, the microparticles are
mixed in a manner that provides for the delivery of active agent to
the patient in a multiphasic manner and/or in a manner that
provides different active agents to the patient at different times,
or a mixture of active agents at the same time. For example,
secondary antibiotics, vaccines, or any desired active agent,
either in microparticle form or in conventional, unencapsulated
form can be blended with a primary active agent and provided to the
patient.
[0090] The microparticles are preferably suspended in the injection
vehicle at a concentration of greater than about 30 mg/ml. In one
embodiment, the microparticles are suspended at a concentration of
from about 150 mg/ml to about 300 mg/ml. In another embodiment, the
microparticles are suspended at a concentration of from about 100
mg/ml to about 400 mg/ml. However, it should be understood that the
invention is not limited to a particular concentration.
[0091] The aqueous injection vehicle preferably has a viscosity of
at least 20 cp at 20.degree. C. In one embodiment, the injection
vehicle has a viscosity greater than 50 cp and less than 60 cp at
20.degree. C. The viscosity of the injection vehicle preferably
provides injectability of the composition through a needle ranging
in diameter from 18-22 gauge. As known to one skilled in the art,
an 18 gauge regular wall (RW) needle has a nominal inner diameter
(ID) of 0.033 in., and a 22 gauge regular wall needle has a nominal
inner diameter of 0.016 in.
[0092] The injection vehicle may comprise a viscosity enhancing
agent. A preferred viscosity enhancing agent is sodium
carboxymethyl cellulose, although other suitable viscosity
enhancing agents may also be used. The injection vehicle may also
comprise a density enhancing agent that increases the density of
the injection vehicle. A preferred density enhancing agent is
sorbitol, although other suitable density enhancing agents may also
be used. The injection vehicle may also comprise a tonicity
adjusting agent to adjust the tonicity to preclude toxicity
problems and improve biocompatibility. A preferred tonicity
adjusting agent is sodium chloride, although other suitable
tonicity adjusting agents may also be used.
[0093] The injection vehicle may also comprise a wetting agent to
ensure complete wetting of the microparticles by the injection
vehicle. Preferred wetting agents include polysorbate 20 (Tween
20), polysorbate 40 (Tween 40), and polysorbate 80 (Tween 80).
[0094] One preferred injection vehicle is an aqueous injection
vehicle that comprises 1.5% sodium carboxymethyl cellulose, 30%
sorbitol, and 0.2% polysorbate 20. Another preferred injection
vehicle is an aqueous injection vehicle that comprises 3% sodium
carboxymethyl cellulose, 0.9% saline, and 0.1% polysorbate 20.
Example 7
1 Kg Process
[0095] A process for preparing microparticles containing
risperidone as the active agent will now be described. The
following 1 Kg process (400 grams of active agent and 600 grams of
polymer) is for a theoretical drug loading of the microparticles of
40%. The actual drug loading that is achieved by the process
described below ranges from about 35% to about 39%.
[0096] A drug solution is prepared by dissolving 400 grams of
risperidone (Janssen Pharmaceutica, Beerse, Belgium) in 1267 grams
of benzyl alcohol to form a 24 wt. % drug solution. A polymer
solution is formed by dissolving 600 grams of MEDISORB.RTM. 7525 DL
polymer (Alkermes, Inc., Blue Ash, Ohio) in 3000 grams of ethyl
acetate to form a 16.7 wt. % polymer solution. The drug solution
and the polymer solution are combined to form a first,
discontinuous phase.
[0097] The second, continuous phase is prepared by preparing a 30
liter solution of 1% PVA, the PVA acting as an emulsifier. To this
is added 2086 grams of ethyl acetate to form a 6.5 wt. % solution
of ethyl acetate.
[0098] The two phases are combined using a static mixer, such as a
1/2'' Kenics static mixer available from Chemineer, Inc., North
Andover, Mass. A total flow rate of 3 L/min generally provides
microparticle size distributions with a mass median diameter (MMD)
in the range of about 80-90.mu.. The ratio of continuous phase to
discontinuous phase is 5:1 (v/v). The length of the static mixer
can vary from about 9 inches to about 88 inches. Lengths greater
than about 48 inches results in the greatest percent yield in a
microparticle size range of 25-150.mu..
[0099] The quench liquid is 2.5% solution of ethyl acetate and
water-for-injection (WFI) at 5-10.degree. C. The volume of the
quench liquid is 0.25 L per gram of batch size. The quench step is
carried out for a time period greater than about 4 hours, with
stirring of the microparticles in the quench tank.
[0100] After completion of the quench step, the microparticles are
transferred to a collecting, de-watering, and drying device. The
microparticles are rinsed using a chilled (approximately 5.degree.
C.) 17 liter 25% ethanol solution. The microparticles are dried,
and then re-slurried in a re-slurry tank using a 25% ethanol
solution (extraction medium) maintained at a temperature lower than
the T.sub.g (glass transition temperature) of the microparticles.
The microparticles are then transferred back to the quench tank for
washing for a time period of at least 6 hours with another
extraction medium (25% ethanol solution) that is maintained at a
temperature higher than the T.sub.g of the microparticles. The
T.sub.g of the microparticles is about 18.degree. C. (about room
temperature), and the temperature of the extraction medium in the
quench tank is greater than about 18.degree. C., preferably
25.degree..+-.1.degree. C.
[0101] The microparticles are transferred back to the collecting,
de-watering, and drying device for de-watering and final drying.
Drying continues for a time period greater than about 16 hours.
CONCLUSION
[0102] While various embodiments of the present invention have been
described above, it should be understood that they have been
presented by way of example only, and not limitation. The present
invention is not limited to controlled release microparticle
injectable suspensions, nor is it limited to a particular active
agent, polymer or solvent, nor is the present invention limited to
a particular scale or batch size. Thus, the breadth and scope of
the present invention should not be limited by any of the
above-described exemplary embodiments, but should be defined only
in accordance with the following claims and their equivalents.
* * * * *