U.S. patent application number 12/949149 was filed with the patent office on 2011-05-19 for methods and compositions for soft tissue repair.
This patent application is currently assigned to AFFINERGY, INC.. Invention is credited to Hanne Gron, Paul Theodore Hamilton, Jonathan Allen Hodges, Michelle Steffen Jansen, Shrikumar Ambujakshan Nair, Ganesan Sathya.
Application Number | 20110117168 12/949149 |
Document ID | / |
Family ID | 44011447 |
Filed Date | 2011-05-19 |
United States Patent
Application |
20110117168 |
Kind Code |
A1 |
Sathya; Ganesan ; et
al. |
May 19, 2011 |
METHODS AND COMPOSITIONS FOR SOFT TISSUE REPAIR
Abstract
Compositions and methods for tissue repair are provided
including cell binding peptides and growth factor binding peptides.
The cell binding peptides bind to one or more of stem cells,
fibroblasts, or endothelial cells. The growth factor binding
peptides include platelet derived growth factor (PDGF) binding
peptides and growth differentiation factor (GDF) binding peptides.
The tissue for repair includes tendon, muscle, connective tissue,
ligament, cardiac tissue, vascular tissue, or dermis. Implantable
devices for tissue repair are provided to which the cell and growth
factor binding peptides are attached, such as acellular
extracellular matrix having attached binding peptide.
Inventors: |
Sathya; Ganesan; (Cary,
NC) ; Jansen; Michelle Steffen; (Durham, NC) ;
Hamilton; Paul Theodore; (Cary, NC) ; Hodges;
Jonathan Allen; (Durham, NC) ; Nair; Shrikumar
Ambujakshan; (Cary, NC) ; Gron; Hanne;
(Durham, NC) |
Assignee: |
AFFINERGY, INC.
Research Triangle Park
NC
|
Family ID: |
44011447 |
Appl. No.: |
12/949149 |
Filed: |
November 18, 2010 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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61262353 |
Nov 18, 2009 |
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61368849 |
Jul 29, 2010 |
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61370723 |
Aug 4, 2010 |
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Current U.S.
Class: |
424/423 ;
424/78.19; 424/78.3; 514/8.2; 514/8.9; 525/54.1; 530/322; 530/326;
530/327; 530/328; 530/353; 530/356; 530/357 |
Current CPC
Class: |
A61L 27/427 20130101;
A61K 47/42 20130101; A61K 47/6957 20170801; A61K 38/10 20130101;
A61P 9/00 20180101; A61L 2300/414 20130101; A61P 21/00 20180101;
A61K 47/02 20130101; A61K 47/64 20170801; A61P 43/00 20180101; A61L
27/425 20130101; A61P 19/04 20180101; A61L 27/54 20130101; A61P
17/00 20180101; A61P 19/00 20180101; A61L 27/58 20130101; A61P
17/02 20180101; A61K 9/0024 20130101; A61L 2430/02 20130101; A61P
19/08 20180101 |
Class at
Publication: |
424/423 ;
530/327; 530/326; 530/328; 530/356; 530/357; 530/353; 530/322;
525/54.1; 514/8.2; 514/8.9; 424/78.19; 424/78.3 |
International
Class: |
A61K 9/00 20060101
A61K009/00; C07K 7/08 20060101 C07K007/08; C07K 7/06 20060101
C07K007/06; C07K 19/00 20060101 C07K019/00; C07K 9/00 20060101
C07K009/00; C08G 63/91 20060101 C08G063/91; A61K 38/39 20060101
A61K038/39; A61K 38/17 20060101 A61K038/17; A61K 38/02 20060101
A61K038/02; A61K 31/785 20060101 A61K031/785; A61F 2/10 20060101
A61F002/10; A61F 2/08 20060101 A61F002/08; A61F 2/12 20060101
A61F002/12; A61P 43/00 20060101 A61P043/00; A61P 9/00 20060101
A61P009/00; A61P 17/00 20060101 A61P017/00; A61P 19/04 20060101
A61P019/04 |
Goverment Interests
GRANT STATEMENT
[0002] The invention was made with government support under Grant
No. 1R43GM083380-01 awarded by the National Institute of General
Medical Sciences, under Grant No. R43GM087751-01 awarded by the
National Institute of General Medical Sciences, and under Grant No.
R44AR053753-02A1 awarded by the National Institute of Arthritis and
Musculoskeletal and Skin Diseases. The government has certain
rights in the invention.
Claims
1. A platelet derived growth factor (PDGF) binding peptide
comprising a sequence selected from the group consisting of SEQ ID
NOs: 25, 28-33, 36, 38, 39, and peptide sequence motifs #1-5;
conservatively substituted variants of SEQ ID NOs: 25, 28-33, 36;
and variants having at least 70% sequence identity to SEQ ID NOs:
25, 28-33, 36; wherein the variant PDGF binding peptide
substantially retains the ability to bind PDGF.
2. The PDGF binding peptide of claim 1, wherein the PDGF binding
peptide comprises one or more modifications to the N-terminus,
peptide C-terminus, or within the peptide amino acid sequence,
wherein the modification is selected from the group consisting of
aldehyde group, hydroxyl group, thiol group, amino group, amino
acids, lysine, cysteine, acetyl group, polymers, synthetic
polymers, polyethers, poly(ethylene glycol) ("PEG"), an 11 unit
polyethylene glycol ("PEG10"), and a 1 unit polyethylene glycol
("mini-PEG" or "MP"), and combinations thereof.
3. An implantable device for tissue repair comprising a polymer
having one or more covalently attached growth factor binding
peptides, wherein the growth factor binding peptide is a platelet
derived growth factor (PDGF) binding peptide or a growth
differentiation factor (GDF) binding peptide.
4. The implantable device of claim 3, wherein the PDGF binding
peptide comprises a sequence selected from the group consisting of
a sequence set forth in SEQ ID NOs: 25, 28-33, 36, 38, 39 and
peptide sequence motifs #1-5, conservatively substituted variants
of SEQ ID NOs: 25, 28-33, 36, and variants having at least 70%
sequence identity to SEQ ID NOs: 25, 28-33, 36, wherein the variant
PDGF binding peptide substantially retains the ability to bind
PDGF, and wherein the GDF binding peptide comprises selected from
the group consisting of a sequence set forth in SEQ ID NOs: 40-43,
conservatively substituted variants of SEQ ID NOs: 40-42, and
variants having at least 70% sequence identity to SEQ ID NOs:
40-42, wherein the variant GDF binding peptide substantially
retains the ability to bind GDF
5. The implantable device of claim 3, wherein the growth factor
binding peptide is attached to the polymer with or without a
spacer.
6. The implantable device of claim 3, wherein the polymer is a
biopolymer selected from the group consisting of a collagen, an
injectable collagen, a keratin, a silk, a polysaccharide, an
agarose, a dextran, a cellulose derivative, an oxidized cellulose,
an oxidized regenerated cellulose, a carboxymethylcellulose, a
hydroxypropylmethylcellulose, a chitosan, a chitin, a hyaluronic
acid, and derivatives and combinations thereof.
7. The implantable device of claim 3, wherein the polymer is a
synthetic polymer selected from the group consisting of polymaleic
anhydride having molecular weight of about 5,000 Dalton or less and
a block co-polymer of polymaleic anhydride having molecular weight
of about 5,000 Dalton or less and a co-polymer comprising a
biodegradable functionality, wherein the co-polymer is selected
from the group consisting of polylactic acid, polyglycolic acid,
polylactic-co-glycolic acid, polycaprolactone,
poly-3-hydroxybutyrate, poly(p-dioxanone) and copolymers thereof,
polyhydroxyalkanoate, poly(propylene fumarate), poly(ortho esters),
and polyanhydrides, and combinations thereof.
8. The implantable device of claim 6 or 7, wherein the implantable
device comprising the polymer is selected from the group consisting
of a gel, a hydrogel, an injectable material, an extracellular
matrix, a decellularized tissue, a dermal matrix, an acellular
human dermis, an acellular porcine dermis, an acellular bovine
dermis, a porcine small intestinal submucosa (SIS), an acellular
myocardium, a cardiac patch, a decellularized vascular conduit, a
surgical mesh, a skin graft, a dural graft, a graft for foot ulcer
repair, a hernia repair graft, a graft for abdominal repair, a
tendon wrap, a tendon augmentation graft, a graft for rotator cuff
repair, a graft or mesh for breast reconstruction, a composite
surgical mesh comprising a synthetic polymer and a biopolymer, and
derivatives and combinations thereof.
9. A method for tissue repair comprising delivering to a subject an
implantable device for tissue repair, wherein the implantable
device comprises a polymer having one or more covalently attached
growth factor binding peptides, wherein the growth factor binding
peptide is a platelet derived growth factor (PDGF) binding peptide
or a growth differentiation factor (GDF) binding peptide, and
wherein the implantable device serves as a scaffold for tissue
repair.
10. The method of claim 9, wherein the PDGF binding peptide
comprises a sequence selected from the group consisting of a
sequence set forth in SEQ ID NOs: 25, 28-33, 36, 38, 39 and peptide
sequence motifs #1-5, conservatively substituted variants of SEQ ID
NOs: 25, 28-33, 36, and variants having at least 70% sequence
identity to SEQ ID NOs: 25, 28-33, 36, wherein the variant PDGF
binding peptide substantially retains the ability to bind PDGF, and
wherein the GDF binding peptide comprises selected from the group
consisting of a sequence set forth in SEQ ID NOs: 40-43,
conservatively substituted variants of SEQ ID NOs: 40-42, and
variants having at least 70% sequence identity to SEQ ID NOs:
40-42, wherein the variant GDF binding peptide substantially
retains the ability to bind GDF.
11. The method of claim 9, wherein the polymer is a biopolymer
selected from the group consisting of a collagen, an injectable
collagen, a keratin, a silk, a polysaccharide, an agarose, a
dextran, a cellulose derivative, an oxidized cellulose, an oxidized
regenerated cellulose, a carboxymethylcellulose, a
hydroxypropylmethylcellulose, a chitosan, a chitin, a hyaluronic
acid, and derivatives and combinations thereof.
12. The method of claim 9, wherein the polymer is a synthetic
polymer selected from the group consisting of polymaleic anhydride
having molecular weight of about 5,000 Dalton or less and a block
co-polymer of polymaleic anhydride having molecular weight of about
5,000 Dalton or less and a co-polymer comprising a biodegradable
functionality, wherein the co-polymer is selected from the group
consisting of polylactic acid, polyglycolic acid,
polylactic-co-glycolic acid, polycaprolactone,
poly-3-hydroxybutyrate, poly(p-dioxanone) and copolymers thereof,
polyhydroxyalkanoate, poly(propylene fumarate), poly(ortho esters),
and polyanhydrides, and combinations thereof.
13. The method of claim 11 or 12, wherein the implantable device
comprising the polymer is selected from the group consisting of a
gel, a hydrogel, an injectable material, an extracellular matrix, a
decellularized tissue, a dermal matrix, an acellular human dermis,
an acellular porcine dermis, an acellular bovine dermis, a porcine
small intestinal submucosa (SIS), an acellular myocardium, a
cardiac patch, a decellularized vascular conduit, a surgical mesh,
a skin graft, a dural graft, a graft for foot ulcer repair, a
hernia repair graft, a graft for abdominal repair, a tendon wrap, a
tendon augmentation graft, a graft for rotator cuff repair, a graft
or mesh for breast reconstruction, a composite surgical mesh
comprising a synthetic polymer and a biopolymer, and derivatives
and combinations thereof.
14. The method of claim 9, wherein the tissue for repair comprises
any one or more of tendon, muscle, connective tissue, ligament,
cardiac tissue, vascular tissue, or dermis.
15. A method for capturing growth factors onto an implantable
device for tissue repair, comprising: contacting a sample
comprising growth factors with the implantable device, wherein the
implantable device comprises a polymer having one or more
covalently attached growth factor binding peptides, wherein the
growth factor binding peptide is a PDGF binding peptide or a GDF
binding peptide, and wherein the growth factor comprised in the
sample is captured onto the implantable device through binding to
the attached growth factor binding peptide.
16. The method of claim 15, wherein the PDGF binding peptide
comprises a sequence selected from the group consisting of a
sequence set forth in SEQ ID NOs: 25, 28-33, 36, 38, 39 and peptide
sequence motifs #1-5, conservatively substituted variants of SEQ ID
NOs: 25, 28-33, 36, and variants having at least 70% sequence
identity to SEQ ID NOs: 25, 28-33, 36, wherein the variant PDGF
binding peptide substantially retains the ability to bind PDGF, and
wherein the GDF binding peptide comprises selected from the group
consisting of a sequence set forth in SEQ ID NOs: 40-43,
conservatively substituted variants of SEQ ID NOs: 40-42, and
variants having at least 70% sequence identity to SEQ ID NOs:
40-42, wherein the variant GDF binding peptide substantially
retains the ability to bind GDF.
17. The method of claim 15, wherein the sample comprising growth
factor comprises bone marrow, allogeneic stem cells, adipose
tissue, stromal vascular fraction of adipose tissue, blood, blood
products, platelets, platelet-rich plasma (PRP), umbilical cord
blood, embryonic tissues, placenta, amniotic epithelial cells,
tissue punch, omentum, recombinant GDF, recombinant PDGF, or a
homogeneous or heterogeneous population of cultured cells, or
combinations or derivatives thereof.
18. The method of claim 15, wherein the polymer is a biopolymer
selected from the group consisting of a collagen, an injectable
collagen, a keratin, a silk, a polysaccharide, an agarose, a
dextran, a cellulose derivative, an oxidized cellulose, an oxidized
regenerated cellulose, a carboxymethylcellulose, a
hydroxypropylmethylcellulose, a chitosan, a chitin, a hyaluronic
acid, and derivatives and combinations thereof.
19. The method of claim 15, wherein the polymer is a synthetic
polymer selected from the group consisting of polymaleic anhydride
having molecular weight of about 5,000 Dalton or less and a block
co-polymer of polymaleic anhydride having molecular weight of about
5,000 Dalton or less and a co-polymer comprising a biodegradable
functionality, wherein the co-polymer is selected from the group
consisting of polylactic acid, polyglycolic acid,
polylactic-co-glycolic acid, polycaprolactone,
poly-3-hydroxybutyrate, poly(p-dioxanone) and copolymers thereof,
polyhydroxyalkanoate, poly(propylene fumarate), poly(ortho esters),
and polyanhydrides, and combinations thereof.
20. The method of claim 18 or 19, wherein the implantable device
comprising the polymer is selected from the group consisting of a
gel, a hydrogel, an injectable material, an extracellular matrix, a
decellularized tissue, a dermal matrix, an acellular human dermis,
an acellular porcine dermis, an acellular bovine dermis, a porcine
small intestinal submucosa (SIS), an acellular myocardium, a
cardiac patch, a decellularized vascular conduit, a surgical mesh,
a skin graft, a dural graft, a graft for foot ulcer repair, a
hernia repair graft, a graft for abdominal repair, a tendon wrap, a
tendon augmentation graft, a graft for rotator cuff repair, a graft
or mesh for breast reconstruction, a composite surgical mesh
comprising a synthetic polymer and a biopolymer, and derivatives
and combinations thereof.
21. A method for tissue repair, comprising: contacting a sample
comprising growth factor with an implantable device comprising a
polymer having one or more covalently attached growth factor
binding peptides, wherein the growth factor binding peptide is a
PDGF binding peptide or a GDF binding peptide, wherein the growth
factors comprised in the sample are captured onto the implantable
device through binding to the attached growth factor binding
peptide; and delivering to a subject the implantable device for
tissue repair.
22. The method of claim 21, wherein the PDGF binding peptide
comprises a sequence selected from the group consisting of a
sequence set forth in SEQ ID NOs: 25, 28-33, 36, 38, 39 and peptide
sequence motifs #1-5, conservatively substituted variants of SEQ ID
NOs: 25, 28-33, 36, and variants having at least 70% sequence
identity to SEQ ID NOs: 25, 28-33, 36, wherein the variant PDGF
binding peptide substantially retains the ability to bind PDGF, and
wherein the GDF binding peptide comprises selected from the group
consisting of a sequence set forth in SEQ ID NOs: 40-43,
conservatively substituted variants of SEQ ID NOs: 40-42, and
variants having at least 70% sequence identity to SEQ ID NOs:
40-42, wherein the variant GDF binding peptide substantially
retains the ability to bind GDF
23. The method of claim 21, wherein the sample comprising growth
factor comprises bone marrow, allogeneic stem cells, adipose
tissue, stromal vascular fraction of adipose tissue, blood, blood
products, platelets, platelet-rich plasma (PRP), umbilical cord
blood, embryonic tissues, placenta, amniotic epithelial cells,
tissue punch, omentum, recombinant GDF, recombinant PDGF, or a
homogeneous or heterogeneous population of cultured cells, or
combinations or derivatives thereof.
24. The method of claim 21, wherein the polymer is a biopolymer
selected from the group consisting of a collagen, an injectable
collagen, a keratin, a silk, a polysaccharide, an agarose, a
dextran, a cellulose derivative, an oxidized cellulose, an oxidized
regenerated cellulose, a carboxymethylcellulose, a
hydroxypropylmethylcellulose, a chitosan, a chitin, a hyaluronic
acid, and derivatives and combinations thereof.
25. The method of claim 21, wherein the polymer is a synthetic
polymer selected from the group consisting of polymaleic anhydride
having molecular weight of about 5,000 Dalton or less and a block
co-polymer of polymaleic anhydride having molecular weight of about
5,000 Dalton or less and a co-polymer comprising a biodegradable
functionality, wherein the co-polymer is selected from the group
consisting of polylactic acid, polyglycolic acid,
polylactic-co-glycolic acid, polycaprolactone,
poly-3-hydroxybutyrate, poly(p-dioxanone) and copolymers thereof,
polyhydroxyalkanoate, poly(propylene fumarate), poly(ortho esters),
and polyanhydrides, and combinations thereof.
26. The method of claim 24 or 25, wherein the implantable device
comprising the polymer is selected from the group consisting of a
gel, a hydrogel, an injectable material, an extracellular matrix, a
decellularized tissue, a dermal matrix, an acellular human dermis,
an acellular porcine dermis, an acellular bovine dermis, a porcine
small intestinal submucosa (SIS), an acellular myocardium, a
cardiac patch, a decellularized vascular conduit, a surgical mesh,
a skin graft, a dural graft, a graft for foot ulcer repair, a
hernia repair graft, a graft for abdominal repair, a tendon wrap, a
tendon augmentation graft, a graft for rotator cuff repair, a graft
or mesh for breast reconstruction, a composite surgical mesh
comprising a synthetic polymer and a biopolymer, and derivatives
and combinations thereof.
27. The method of claim 21, wherein the tissue for repair comprises
any one or more of tendon, muscle, connective tissue, ligament,
cardiac tissue, vascular tissue, or dermis.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application claims the benefit of U.S. Provisional
Application No. 61/262,353, filed Nov. 18, 2009; U.S. Provisional
Application No. 61/368,849, filed Jul. 29, 2010; and U.S.
Provisional Application No. 61/370,723, filed Aug. 4, 2010, each of
which is hereby incorporated in its entirety by reference
herein.
FIELD
[0003] The presently disclosed subject matter relates to the
capture of cells and growth factors onto implantable devices for
tissue repair.
BACKGROUND
[0004] Multipotent stem cells are known to play a role in healing
and repair in response to trauma, disease or disorder. Stem cell
mediated repair and healing are achieved by proliferation and
differentiation of the stem cells into specialized cell types. For
example, mesenchymal stem cells can differentiate into cell types
such as bone, cartilage, fat, ligament, muscle, and tendon. In the
case of defects in bone, mesenchymal stem cells from the bone
marrow, periosteum, and surrounding soft tissue proliferate and
differentiate into specialized bone cells. Stem cells can be
obtained from embryonic or adult tissues of humans or other
animals. As a result of the healing activity of stem cells, much
focus has been placed on using stem cells as a treatment to aid in
the remodeling of damaged tissue into healthy tissue.
[0005] In addition to stem cells, certain growth factors have shown
clinical benefit in treatment of bone defects, injuries, disorders,
or diseases. Growth and differentiation factors (GDFs) are members
of the family of growth factors belonging to the family of bone
morphogenetic proteins (BMPs). GDF-5, GDF-6, and GDF-7 (also known
as BMP-14, BMP-13, and BMP-12, respectively) are involved in
fibrous connective tissue development and healing, as GDFs
stimulate production of fibrous connective tissue in vitro and in
vivo. However, use of exogenous GDF to aid in tissue repair has
been associated with ectopic differentiation of joints, tendon,
cartilage, and bone.
[0006] Platelet derived growth factor-BB (PDGF-BB) is known to be
involved in wound healing (Pierce et al., 1992, Am. J. Pathol.,
140:1375-88) and a product containing PDGF-BB has been approved by
the FDA for wound healing indications. The data support the safety
and benefits of PDGF-BB in healing diabetic ulcers (Smiell et al.,
1999, Wound Rep. Reg., 7:335-46). However, PDGF-BB therapy requires
repeated applications to achieve clinical efficacy, and PDGF is a
potent initiator of fibroblast proliferation which has been linked
to tumor growth (Alvarez et al., 2006, Mayo Clin. Proc.,
81:1241-57).
[0007] In addition to stem cells, fibroblast cells have a role in
soft tissue repair. Hernia repair is one of the most common
surgical procedures world-wide, with over 20 million repairs
performed each year (Kingsnorth, A. and K. LeBlanc, Lancet, 2003,
362:1561-71). In the US there are approximately 100,000 incisional
hernia repairs performed annually costing an estimated 1.7 billion
dollars (Finan et al., Hernia, 2009, 13:173-82). Despite advances,
recurrence rates remain high and range from 3-60% with an average
rate of 25% for an initial repair and 44% after a second repair
(Afifi, R. Y., Hernia, 2005, 9:310-5; Gray et al., Am J Surg, 2008,
196:201-6). Biocompatible materials have triggered a rapid
evolution of hernia repair techniques over the past 10 years.
High-tension fascial suturing to strengthen the abdominal wall has
been replaced by low-tension repair using biocompatible synthetic
mesh (Luijendijk et al., N Engl J Med, 2000, 343:392-98; Flum et
al., Ann Surg, 2003, 237:129-35). While a modest improvement over
basic suturing, synthetic mesh harbors all the potential pitfalls
of implanting a permanent foreign body: adhesions, potential
infection, chronic pain, and subsequent mesh removal (Flum et al.,
Ann Surg, 2003, 237:129-35; Conze et al., Langenbecks Arch Surg,
2007. 392:453-37). Allograft and xenograft materials such as, for
example, acellular dermal matrix (ADM) and porcine small intestine
submucosa have emerged as favorable alternatives to synthetics,
especially in patients with comorbidities, for many types of soft
tissue repair including wound, abdominal wall, tendon, breast, dura
matter, and rotator cuff repair (Diaz et al., Am Surg, 2006,
72:1181-88; Kim et al., Am J Surg, 2006, 192:705-9; Kish et al., Am
Surg, 2005, 71:1047-50; Butler, C. E., Clin Plastic Surg, 2006,
33:199-211; Badylak, S. F., Biomaterials, 2007, 28:3587-93; Longo
et al., British Medical Bulletin, 2010, 94:165-88), maintaining an
intact elastin lattice, as well as channels for capillary
microvascularization. These collagen-based materials promote key
components of wound healing and are bioabsorbable. However,
complication rates of 24% with recurrence being the most common
complication have been reported with these materials, and design
improvements are needed (Gupta, A., et al., Hernia, 2006,
10:419-25; Misra, S., et al., Hernia, 2008, 12:247-50). Wound
breaking strength represents the amount of force a surgical wound
can withstand before failing, and failure occurs when there is a
deficient quantity and quality of tissue repair (Franz, M. G., Surg
Clin North Am, 2008, 88:1-15, vii). Previous studies have suggested
that wound repair integrity reaches a normal breaking strength in
30 days (Franz et al., J Surg Res, 2001, 97: 109-16; Robson, M. C.,
Surg Clin North Am, 2003, 83:557-69). Fibroblasts are responsible
for collagen synthesis and deposition and recovery of wound
breaking strength (Franz, M. G., Surg Clin North Am, 2008, 88:1-15,
vii). Two days post surgery the inflammatory response subsides and
fibroblasts infiltrate the wound, out numbering other cell types by
day 4 (Dubay, D. A. and M. G. Franz, Surg Clin North Am, 2003,
83:463-81). Wounds are increasingly challenged during the recovery
period as patients return to normal activity. Therefore, a medical
device that can become populated with fibroblasts and vascularize
faster than other bioprosthetics would reduce the recovery time and
increase healing rates to improve repair outcomes.
[0008] The leading cause of death in the world today is
cardiovascular disease (CVD)(Lopez et al., 2006, 367:1747-57), and
the vast majority of CVD is related to impairment of blood flow
through diseased atherosclerotic arteries. Stenting and bypass
surgery are the most common interventions used to treat occluded
arteries. Ideally, the patients own internal mammary artery or the
saphenous vein are used as the graft material, but often autologous
tissue conduits are not available (Faries et al., J Vasc Surg,
2000, 31:1119-27; Zhang et al., J Cell Mol Med, 2007, 11:945-57).
Alternatively, synthetic conduits such as expanded
polytetrafluoroethylene (ePTFE) or polyethylene terephthalate
(Dacron) are used. For large caliber arteries (.gtoreq.8 mm) Dacron
grafts have largely been successful. In contrast, ePTFE, which is
commonly used for small caliber arteries (.ltoreq.6 mm), has a high
incidence of failure due to intimal hyperplasia and ongoing surface
thrombogenicity (Chlupac et al., Physiol Res, 2009, 58 Suppl
2:S119-39; Zilla et al., Biomaterials, 2007, 28:5009-27). The
absence of a selectively permeable and thrombo-resistant
endothelium is the main reason for the failure of medium to
small-caliber prosthetic vascular grafts (Zhang et al., J Cell Mol
Med, 2007, 11:945-57). Ingrowth of a vascular graft from
neighboring endothelial cells (EC), and colonization of circulating
endothelial progenitor cells (EPC) have resulted in
endothelialization of vascular grafts in animal models (Zilla et
al., Biomaterials, 2007, 28:5009-27; Shi et al., Blood, 1998, p.
362-67). Successful pre-clinical studies have not translated to the
clinic in localizing these cell types to grafts to generate a
non-thrombotic surface (Walter et al., Circulation, 2002, p.
3017-24; Werner et al., Circ Res. 2003, p. e17-24; Bhattacharya et
al., in Blood, 2000, p. 581-5; Kaushal et al., in Nat. Med. 2001,
p. 1035-40; Griese et al., in Circulation, 2003, p. 2710-5).
Furthermore, new tissue engineering technologies are being
developed to generate grafts made of both natural and/or synthetic
scaffold material that promote endothelialization (Amiel et al.,
Tissue Eng, 2006, 12:2355-65; L'Heureux et al., Nat Med, 2006,
12:361-65; Tillman et al., Biomaterials, 2009, 30:583-8). Positive
preclinical and clinical studies involving the seeding of cells at
the luminal surface of prosthetic vascular grafts prior to
implantation supports the concept that ECs and EPCs can improve
functional outcomes in vivo (Bhattacharya et al., in Blood. 2000.
p. 581-5; Deutsch et al., Surgery, 1999, 126:847-55; Meinhart et
al., in Ann Thorac Surg. 2001. p. S327-31; Zilla et al., in J Vasc
Surg. 1994. p. 540-8; Parikh, S. A. and E. R. Edelman, Adv Drug
Deliv Rev, 2000, 42:139-61). However, EC seeding is laborious,
expensive, can introduce contaminants, and is not always possible.
Alternatively, mobilizing EPCs from bone marrow followed by capture
of EPCs on a vascular graft represents an exciting alternative that
eliminates most of the complications associated with cell seeding,
and is currently being explored in the clinic with bare metal
stents (Aoki et al., J Am Coll Cardiol, 2005, 45:1574-9). In animal
models, small numbers of circulating EPCs have been shown to
passively attach to implanted grafts and decrease neointima
formation following vascular injury (Walter et al., in Circulation.
2002. p. 3017-24; Werner et al., in Circ Res. 2003. p. e17-24). A
vascular graft that would promote better endothelialization would
reduce intimal hyperplasia and thrombosis.
[0009] Therefore, while tissue remodeling can theoretically be
achieved by application of cells and/or growth factors at the site
of damaged tissue, several obstacles stand in the way of this
regenerative technology becoming reality. One obstacle is that
cells and/or growth factors injected into many tissues are rapidly
cleared via the lymphatics or vascular drainage. In addition, the
growth factors can have undesirable ectopic effects. Another
obstacle is that the most widely used source of stem cells, bone
marrow aspirate, often provides an inadequate amount of stem cells.
As a result, use of allogeneic stem cells or culturing of stem
cells to increase their number prior to use is frequently still
required.
[0010] Thus, there remains a need for systems to locally bind,
deliver, and retain cells and growth factors to a site of tissue in
need of healing or repair. The presently disclosed subject matter
provides such systems.
SUMMARY
[0011] The presently disclosed subject matter provides compositions
and methods for tissue repair including cell binding peptides and
implantable devices for tissue repair comprising the attached cell
binding peptides. The tissue for repair includes tendon, muscle,
connective tissue, ligament, cardiac tissue, vascular tissue, or
dermis. The cell binding peptides bind to one or more of stem
cells, fibroblasts, or endothelial cells.
[0012] In one embodiment, the presently disclosed subject matter
provides compositions and methods for tissue repair including
growth factor binding peptides and implantable devices for tissue
repair comprising the attached growth factor binding peptides. The
growth factor binding peptides include platelet derived growth
factor (PDGF) binding peptides and growth differentiation factor
(GDF) binding peptides. The tissue for repair includes tendon,
muscle, connective tissue, ligament, cardiac tissue, vascular
tissue, or dermis.
[0013] In one embodiment, the presently disclosed subject matter
provides compositions and methods for tissue repair including
implantable devices for tissue repair comprising the attached cell
binding and more or more of the growth factor binding peptides. The
tissue for repair includes tendon, muscle, connective tissue,
ligament, cardiac tissue, vascular tissue, or dermis.
[0014] In one embodiment, the presently disclosed subject matter
provides a method for tissue repair comprising delivering to a
subject an implantable device comprising an attached cell binding
peptide, wherein the implantable device serves as a scaffold for
tissue repair. In one embodiment, the implantable device being
delivered to the subject for tissue repair further comprises one or
more of the growth factor binding peptides. The tissue for repair
includes tendon, muscle, connective tissue, ligament, cardiac
tissue, vascular tissue, or dermis.
[0015] In one embodiment, the presently disclosed subject matter
provides a method for tissue repair comprising delivering to a
subject an implantable device comprising an attached growth factor
binding peptide, wherein the implantable device serves as a
scaffold for tissue repair. The tissue for repair includes tendon,
muscle, connective tissue, ligament, cardiac tissue, vascular
tissue, or dermis.
[0016] In one embodiment, the presently disclosed subject matter
provides a method for capturing cells onto an implantable device
for tissue repair, the method comprising contacting a sample
comprising cells with the implantable device comprising an attached
cell binding peptide, wherein the cells comprised in the sample are
captured onto the implantable device through binding to the
attached cell binding peptide. In one embodiment, the sample
comprising cells comprises bone marrow, allogeneic stem cells,
adipose tissue, stromal vascular fraction of adipose tissue, blood,
blood products, platelets, platelet-rich plasma (PRP), umbilical
cord blood, embryonic tissues, placenta, amniotic epithelial cells,
tissue punch, omentum, recombinant GDF, recombinant PDGF, or a
homogeneous or heterogeneous population of cultured cells, or
combinations or derivatives thereof. In one embodiment of the
method for capturing cells, the implantable device further
comprises an attached growth factor binding peptide, and the sample
comprising cells also comprises the growth factor which is captured
onto the implantable device through binding to the attached growth
factor binding peptide.
[0017] In one embodiment, the presently disclosed subject matter
provides a method for capturing a growth factor onto an implantable
device for tissue repair, the method comprising contacting a sample
comprising the growth factor with the implantable device comprising
an attached growth factor binding peptide, wherein the growth
factor comprised in the sample is captured onto the implantable
device through binding to the attached growth factor binding
peptide. In one embodiment, the sample comprising a growth factor
comprises bone marrow, allogeneic stem cells, adipose tissue,
stromal vascular fraction of adipose tissue, blood, blood products,
platelets, platelet-rich plasma (PRP), umbilical cord blood,
embryonic tissues, placenta, amniotic epithelial cells, tissue
punch, omentum, recombinant GDF, recombinant PDGF, or a homogeneous
or heterogeneous population of cultured cells, or combinations or
derivatives thereof.
[0018] In one embodiment, the presently disclosed subject matter
provides a method for tissue repair, the method comprising
contacting a sample comprising cells with an implantable device
comprising an attached cell binding peptide, wherein the cells
comprised in the sample are captured onto the implantable device
through binding to the attached cell binding peptide; and
delivering to a subject the implantable device having the captured
cells for tissue repair. In one embodiment, the implantable device
further comprises an attached growth factor binding peptide, the
sample comprising cells also comprises growth factor, and the
growth factor comprised in the sample is captured onto the
implantable device through binding to the attached growth factor
binding peptide. The tissue for repair includes tendon, muscle,
connective tissue, ligament, cardiac tissue, vascular tissue, or
dermis. In one embodiment, the sample comprises bone marrow,
allogeneic stem cells, adipose tissue, stromal vascular fraction of
adipose tissue, blood, blood products, platelets, platelet-rich
plasma (PRP), umbilical cord blood, embryonic tissues, placenta,
amniotic epithelial cells, tissue punch, omentum, recombinant GDF,
recombinant PDGF, or a homogeneous or heterogeneous population of
cultured cells, or combinations or derivatives thereof.
[0019] In one embodiment, the presently disclosed subject matter
provides a method for tissue repair, the method comprising
contacting a sample comprising growth factor with an implantable
device comprising an attached growth factor binding peptide which
captures the growth factor comprised in the sample onto the
implantable device; and delivering to a subject the implantable
device for tissue repair. The tissue for repair includes tendon,
muscle, connective tissue, ligament, cardiac tissue, vascular
tissue, or dermis. In one embodiment, the sample comprises bone
marrow, allogeneic stem cells, adipose tissue, stromal vascular
fraction of adipose tissue, blood, blood products, platelets,
platelet-rich plasma (PRP), umbilical cord blood, embryonic
tissues, placenta, amniotic epithelial cells, tissue punch,
omentum, recombinant GDF, recombinant PDGF, or a homogeneous or
heterogeneous population of cultured cells, or combinations or
derivatives thereof.
BRIEF DESCRIPTION OF THE DRAWINGS
[0020] FIG. 1 is a schematic diagram depicting one method for
covalently attaching a binding peptide to a substrate comprising
amino functional groups.
[0021] FIG. 2 is a schematic diagram depicting one method for
covalently attaching a binding peptide to a substrate comprising
amino functional groups.
[0022] FIG. 3 is a schematic diagram depicting methods for
covalently attaching a binding peptide to a substrate having an
amino functional group.
[0023] FIG. 4 is a schematic diagram depicting one method for
covalently attaching a binding peptide to a substrate comprising
amino functional groups.
[0024] FIG. 5 is a schematic diagram depicting one method for
covalently attaching a binding peptide to a substrate comprising
amino functional groups.
[0025] FIG. 6 is a schematic diagram depicting the chemistry for
covalently attaching a binding peptide to a polyanhydride polymer,
polymaleic anhydride (PMA), through the reactive amines on the
peptide.
[0026] FIG. 7 is a schematic diagram depicting exemplary chemistry
for covalently attaching a binding peptide to chitosan.
[0027] FIG. 8 is a schematic diagram depicting exemplary chemistry
for covalently attaching a binding peptide to chitosan.
[0028] FIG. 9 is a schematic diagram depicting exemplary chemistry
for covalently attaching a binding peptide to hyaluronic acid.
[0029] FIG. 10 is a schematic diagram depicting exemplary chemistry
for covalently attaching a binding peptide to hyaluronic acid.
[0030] FIG. 11 is a schematic diagram depicting exemplary chemistry
for introducing an amino functional group on cellulose for
subsequent covalent attachment of a binding peptide.
[0031] FIG. 12 is a schematic diagram depicting exemplary chemistry
for covalently attaching a binding peptide to oxidized
cellulose.
[0032] FIG. 13 is a schematic diagram depicting one method for
covalently attaching more than one binding peptide to a substrate
comprising amino functional groups.
[0033] FIG. 14 is a table showing an alignment of cell binding
peptides from a phage display library selection.
[0034] FIG. 15 is a bar graph showing the ability of stem cell
binding peptide SEQ ID NO: 4 to specifically bind human mesenchymal
stem cells (hMSCs) from bone marrow compared to a number of other
cells types including human adipose-derived mesenchymal stem cells
(hASCs), human dermal fibroblasts, rodent MSCs, red blood cells
(RBCs), monocytes, lymphocytes and granulocytes. The y axis shows
biotinylated stem cell binding peptide SEQ ID NO: 4 reactivity as
percent positivity relative to Neutravidin-PE staining without the
addition of biotinylated peptide.
[0035] FIGS. 16A-16C are graphs showing the ability of cell binding
peptide SEQ ID NO: 4 to bind endothelial cells compared to other
cell types. The cell binding peptide was incubated with human
umbilical vein endothelial cells (HUVECs), endothelial colony
forming cells (ECFCs), umbilical artery smooth muscle cells
(UASMCs) or whole blood cells. The data in FIGS. 16A & 16B show
that SEQ ID NO: 4 cross-reacted strongly with ECFCs and HUVECs,
weakly with UASMCs, and had no cross-reactivity with peripheral
blood cells. The cell binding peptide was assayed for its ability
to selectively isolate endothelial cells versus smooth muscle cells
in the presence of whole blood. The data in FIG. 16C show that the
cell binding peptide isolated 8-fold more HUVECs compared to
UASMCs.
[0036] FIG. 17 is a bar graph showing the ability of biotinylated
stem cell binding peptide SEQ ID NO: 4 ("test") to capture human
MSCs from a homogeneous cultured cell population relative to a
non-binding control peptide ("control"). The capture of MSCs bound
to biotinylated peptide was performed with MILTENYI BIOTEC
Streptavidin microbeads loaded into LS columns.
[0037] FIGS. 18A-18C are flow cytometry histograms of cells showing
selective capture of MSCs on biotinylated stem cell binding peptide
SEQ ID NO: 16 ("test"; panel C) attached to CELLECTION magnetic
beads. The CELLECTION beads have streptavidin coupled to a magnetic
particle through a DNA linker. Three different cell types, human
MSCs, IM-9, and U937 cells were differentially labeled with
CELLTRACKER dye and mixed in a ratio such that the MSCs represented
.about.4% of the starting cell mixture (the percentage of each cell
type in the starting mixture was 38% IM9, 56% U937, and 4% MSC
(panel A). Panel B is a no peptide control.
[0038] FIG. 19 is a bar graph showing the ability of biotinylated
stem cell binding peptide SEQ ID NO: 4 ("test") to capture human
MSCs directly from bone marrow aspirate in comparison to a negative
peptide control and to two separate antibodies against the CD105
stem cell antigen (CD105) and the MSCA-1 stem cell antigen
(MSCA-1), respectively. The capture of MSCs bound to biotinylated
peptide was performed with MILTENYI BIOTEC Streptavidin microbeads
loaded into LS columns. The y axis shows colony forming units
(CFUs) counted after 14 days in culture.
[0039] FIGS. 20A and 20B are images showing the ability of a
collagen sponge having covalently attached stem cell binding
peptide SEQ ID NO: 4 (panel A) to capture cultured human MSCs
labeled with fluorescent CELLTRACKER Green dye compared to an
unmodified collagen sponge (panel B). The stem cell binding peptide
SEQ ID NO: 4 was modified at the carboxyl terminus with a PEG-10
spacer and a lysine residue. After contact with MSCs, sponges were
transferred and incubated with 2% fetal bovine serum. Sponge images
(16 ms, 10.times.) were taken after a 19 hour incubation.
[0040] FIGS. 21A-21C demonstrate the ability of collagen having
covalently attached cell binding peptide SEQ ID NO: 4 to capture
and retain endothelial cells. FIG. 21A shows a peptide dependent
increase in cell retention on peptide-modified collagen, with a
3-fold increase in cell retention for the peptide-modified collagen
over unmodified collagen. The data in FIG. 21B show that the
collagen coating was similar for all the samples shown in FIG. 21A.
Peptide-modified collagen retained 7-fold more HUVECs than
unmodified collagen (FIG. 21C).
[0041] FIGS. 22A-22B are graphs showing that the phenotype,
viability, and anti-thrombogenic protein expression profiles for
endothelial cells are not altered in the presence of collagen
modified with cell binding peptide SEQ ID NO: 4. Cells cultured in
the presence of peptide-modified collagen, collagen with free
peptide, or collagen alone for 24 hours maintained their
endothelial cell phenotype and their ability to secrete
anti-thrombogenic proteins.
[0042] FIG. 23 is a graph showing that HUVECs colonize and
proliferate equally on unmodified and SEQ ID NO: 4 cell binding
peptide-modified collagen.
[0043] FIG. 24 is a graph showing HUVEC retention by SEQ ID NO: 4
cell binding peptide-modified- and unmodified-collagen sponges.
After 20 hours of incubation with the HUVECs, the cell binding
peptide-modified sponge retained 5-fold more cells than the
unmodified collagen sponge.
[0044] FIGS. 25A-25B are graphs showing the ability of collagen
modified with cell binding peptide SEQ ID NO: 4 to capture cells in
flow or under shear stress. Glass cover-slips were coated with
peptide modified collagen or unmodified collagen and seeded with
ECFCs in flow (Panel A) or HUVECs under shear stress (Panel B).
[0045] FIGS. 26A-26D are images of differentiated MSCs captured
from bone marrow aspirate with stem cell binding peptide SEQ ID NO:
4. Following a 21 day incubation in adipocyte differentiation
media, captured MSCs were fixed and stained with Oil Red 0 to
determine the extent of adipogenesis. Panel A shows
undifferentiated MSCs and panel B shows adipocyte differentiated
MSCs. The image of the adipose differentiated cells (panel B)
contains a larger magnification inset where the lipid vacuoles are
clearly visible. Following a 14 day incubation in osteoblast
differentiation media, the captured MSCs were stained with Alizarin
Red S to reveal mineralizing osteoblasts. Panel C shows
undifferentiated MSCs and panel D shows osteoblast differentiated
MSCs.
[0046] FIGS. 27A-27D are images of differentiated MSCs captured
from bone marrow aspirate with a stem cell binding peptide SEQ ID
NO: 4. In FIG. 27, sections from the periphery (panels A and B) or
center (panels C and D) were incubated with an antibody against
aggrecan (ABCAM) (panels B and D) or with secondary detection
reagents only as a control (panels A and C), then counterstained
with DAPI to reveal cell nuclei.
[0047] FIG. 28 is a graph showing enhanced binding of human dermal
fibroblasts to cell binding peptide (SEQ ID NO: 4)-modified
collagen compared to unmodified collagen. The collagen was coated
on a polystyrene microtiter plate.
[0048] FIG. 29 is a graph showing the binding curves for
PDGF-binding peptides where increasing concentrations of PDGF
growth factor are examined. The numbers in FIG. 29 refer to
PDGF-binding peptides SEQ ID NOs: 21-27. "Control" refers to a
peptide known not to bind to PDGF.
[0049] FIG. 30 is a graph showing the binding curves for
PDGF-binding peptides having an N-terminal amino acid tag where
increasing concentrations of PDGF growth factor are examined. The
numbers in FIG. 30 refer to PDGF-binding peptides SEQ ID NOs: 25
and 30-32.
[0050] FIG. 31 is a schematic depiction of truncations of PDGF
binding peptide SEQ ID NO: 25 where the truncated peptides have
been examined for binding to PDGF relative to the full-length
sequence (indicated by a "+" or "-" symbol). The numbers in FIG. 31
refer to peptides SEQ ID NOs: 25 and 33-37.
[0051] FIG. 32 is a graph showing PDGF-BB loading at 10 and 100 nM
on a PDGF binding peptide (SEQ ID NO: 29)-modified collagen sponge
versus an unmodified sponge control. The PDGF binding
peptide-modified sponges bound significantly more PDGF-BB than the
unmodified sponges.
[0052] FIGS. 33A-33B are graphs showing bioactivity of PDGF-BB
after binding to a PDGF binding peptide-modified sponge (SEQ ID NO:
29). Panel A) Tyrosine phosphorylation of the PDGF receptor by
PDGF-BB released from PDGF binding peptide-modified or unmodified
sponges by collagenase. Panel B) BrdU incorporation into NIH-3T3
cells after stimulation with PDGF-BB released by acid elution. U,
unstimulated (far right point on graphs).
DETAILED DESCRIPTION
[0053] The methods and compositions of the presently disclosed
subject matter are described in greater detail herein below.
DEFINITIONS
[0054] While the following terms are believed to be well understood
by one of ordinary skill in the art, the following definitions are
set forth to facilitate explanation of the presently disclosed
subject matter.
[0055] Unless defined otherwise, all technical and scientific terms
used herein have the same meaning as commonly understood to one of
ordinary skill in the art to which the presently disclosed subject
matter belongs.
[0056] Following long-standing patent law convention, the terms
"a", "an", and "the" refer to "one or more" when used in this
application, including the claims. Thus, for example, reference to
"a cell binding peptide" or reference to "a 1 unit polyethylene
glycol ("mini-PEG" or "MP")" includes a plurality of such cell
binding peptides or such polyethylene glycol units, and so
forth.
[0057] The term "adipose tissue" as used herein, for the purposes
of the specification and claims, includes the term "liposuction
aspirate". Therefore, the term "stromal vascular fraction of
adipose tissue" also means "stromal vascular fraction of
liposuction aspirate".
[0058] The cell binding peptides and the growth factor binding
peptides of the presently disclosed subject matter are herein
collectively referred to as the "binding peptides". The term "cell
binding peptide" is used herein, for the purposes of the
specification and claims, to refer to an amino acid chain
comprising a peptide that can bind to a cell and is set forth in
any one of SEQ ID NOs: 1-20 described in Example 1 (i.e., the cell
is the binding "target" of the cell binding peptide). The cell
binding peptides of the presently disclosed subject matter bind one
or more of stem cells, fibroblasts, or endothelial cells. In
addition, the term "stem cell binding peptide" is in some cases
herein used interchangeably, for the purposes of the specification
and claims, with the terms "cell binding peptide" and "endothelial
cell binding peptide" and "fibroblast binding peptide" as certain
of the stem cell binding peptides described in Example 1 also bind
to fibroblast and endothelial cells (see, e.g., Example 3).
[0059] The term "growth factor binding peptide" is used herein, for
the purposes of the specification and claims, to refer to an amino
acid chain comprising a peptide that can bind to a growth factor
(i.e., the growth factor is the binding "target" of the growth
factor binding peptide). In one embodiment, the growth factor is
platelet derived growth factor (PDGF) or growth and differentiation
factor (GDF) (a family of growth factors belonging to the family of
BMPs including GDF-5 (BMP-14), GDF-6 (BMP-13), and GDF-7 (BMP-12)).
In one embodiment, the growth factor is PDGF and the PDGF binding
peptide is set forth in any one of SEQ ID NOs: 25, 28-33, 36, 38,
39 and peptide sequence motifs #1-5 (see Example 14). In one
embodiment, the growth factor is GDF and the GDF binding peptide is
set forth in US Patent Application Publication No. US 2009/0098175
A1 and is set forth therein as one of SEQ ID No's: 1-12 (i.e.,
these are the SEQ ID NO identifiers for the previously published
patent application rather than this current one). In one
embodiment, the GDF binding peptide is set forth in US Patent
Application Publication No. US 2009/0098175A1 and is any one of SEQ
ID NOs: 40-43 shown herein at Table 5.
[0060] The term "substrate" is used, for the purposes of the
specification and claims, to refer to any material that is
biologically compatible with cells and/or growth factors and to
which a binding peptide can be attached for the purpose of
capturing target cells and/or growth factors onto the substrate.
The binding peptide attached to the substrate can be one or more of
a cell binding peptide or a growth factor binding peptide, or
combinations thereof. In one embodiment the substrate is in the
form of an implantable device. Therefore, the terms "substrate" and
"implantable device" are herein used interchangeably, for the
purposes of the specification and claims. In one embodiment, the
implantable device for tissue repair comprises a polymer having an
attached binding peptide. Accordingly, the term "substrate" is used
interchangeably herein with the term "polymer" for the purposes of
the specification and claims when referring to the attachment of a
binding peptide to a "substrate" it is meant that attachment of the
binding peptide is to a polymer comprised in the substrate.
Therefore, the attachment of a binding peptide to a "substrate" is
referring to attachment of the binding peptide to the polymer
comprised in the substrate.
[0061] In one embodiment, the substrate or implantable device can
comprise any material and can be present in any form that is
desirable and conducive to capturing cells onto the substrate such
that the cells retain their native activity such as, for example,
stem cells retaining their ability to differentiate into one or
more cells of mesenchymal tissue lineage. Similarly, the substrate
or implantable device can comprise any material and can be present
in any form that is desirable and conducive to capturing growth
factors onto the substrate such that the growth factors retain
their biological growth factor activity. The term "implantable
device" generally refers to a structure that is introduced into a
human or animal body to restore a function of a damaged tissue or
to provide a new function. Representative implantable devices
include, but are not limited to, a gel, a hydrogel, an injectable
polymeric material, an extracellular matrix, a decellularized
tissue, a dermal matrix, an acellular human dermis, an acellular
porcine dermis, an acellular bovine dermis, a porcine small
intestinal submucosa (SIS), an acellular myocardium, a cardiac
patch, a decellularized vascular conduit, a surgical mesh, a skin
graft, a dural graft, a graft for foot ulcer repair, a hernia
repair graft, a graft for abdominal repair, a tendon wrap, a tendon
augmentation graft, a graft for rotator cuff repair, a graft or
mesh for breast reconstruction, a composite surgical mesh
comprising a synthetic polymer and a biopolymer, and derivatives
and combinations thereof.
[0062] In one embodiment, the implantable device for tissue repair
comprises a polymer having an attached binding peptide. The term
"polymer" is used herein, for the purposes of the specification and
claims, to refer to a biopolymer or a synthetic polymer suitable
for use in the compositions and methods of the presently disclosed
subject matter. In one embodiment, a binding peptide is covalently
attached to the biopolymer. In one embodiment, a binding peptide is
covalently attached to the synthetic polymer. Biopolymers of the of
the presently disclosed subject matter include, by non-limiting
example, a collagen, an injectable collagen, a keratin, a silk, a
polysaccharide, a dextran, an agarose, a cellulose derivative, an
oxidized cellulose, an oxidized regenerated cellulose, a
carboxymethylcellulose, a hydroxypropylmethylcellulose, a chitosan,
a chitin, a hyaluronic acid, and derivatives and combinations
thereof. Synthetic polymers of the presently disclosed subject
matter include, by non-limiting example, a polyanhydride polymer
where the anhydride groups are not present in the backbone of the
polymer and the portion of the polyanhydride polymer chain that
will not be hydrolyzed in vivo is small enough to allow efficient
clearance through the renal system. Polymaleic anhydride (PMA)
having molecular weight of about 5,000 Dalton or less is one
example of a resorbable polyanhydride polymer for the purposes of
the specification and claims. In another example, the synthetic
polymer to which the binding peptide is attached is a block
co-polymer of polymaleic anhydride having molecular weight of about
5,000 Dalton or less and a co-polymer comprising a biodegradable
functionality, wherein the co-polymer is selected from the group
consisting of polylactic acid (PLA), polyglycolic acid (PGA),
polylactic-co-glycolic acid (PLGA), polycaprolactone,
poly-3-hydroxybutyrate, poly(p-dioxanone) and copolymers thereof,
polyhydroxyalkanoate, poly(propylene fumarate), poly(ortho esters),
and polyanhydrides, and combinations thereof.
[0063] The implantable devices for tissue repair of the presently
disclosed subject matter comprise a polymer having an attached
binding peptide. A number of extracellular matrices and composites
of absorbable and non-absorbable materials for soft tissue repair
that comprise one or more of the biopolymers or synthetic polymers
listed herein above are discussed in Grevious et al., Clin Plastic
Surg, 2006, 33:181-97; Butler, C. E., Clin Plastic Surg, 2006,
33:199-211; Badylak, S. F., Biomaterials, 2007, 28:3587-93; and
Longo et al., British Medical Bulletin, 2010, 94:165-88, each of
which is herein incorporated by reference in its entirety. The
extracellular matrices and composites described in the foregoing
articles that comprise one or more of the biopolymers or synthetic
polymers listed herein above are implantable devices to which a
binding peptide of the presently disclosed subject matter is
covalently attached (see, e.g., Example 8).
[0064] The term "attached" in reference to a binding peptide of the
presently disclosed subject matter being "attached" to a polymer
means, for the purposes of the specification and claims, a binding
peptide being immobilized on the substrate by means that will
enable capture of the binding peptide target onto the polymer. In
the case of the cell binding peptides, the cell binding peptides
can be "attached" to the polymer by means that will enable capture
of cells onto the polymer such that the stem cells retain their
native activity. In the case of the growth factor binding peptides,
the growth factor binding peptides can be "attached" to the polymer
by any means that will enable capture of growth factors onto the
implantable device such that the growth factors retain their
biological growth factor activity. A binding peptide can be
attached to a polymer by any one of covalent bonding, non-covalent
bonding including, one or more of hydrophobic interactions, Van der
Waals forces, hydrogen bonds, ionic bonds, magnetic force, or
avidin-, streptavidin-, and Neutravidin-biotin bonding.
[0065] The binding peptides of the presently disclosed subject
matter can include naturally occurring amino acids, synthetic amino
acids, genetically encoded amino acids, non-genetically encoded
amino acids, and combinations thereof; however, an antibody is
specifically excluded from the scope and definition of a binding
peptide of the presently disclosed subject matter. A binding
peptide used in accordance with the presently disclosed subject
matter can be produced by chemical synthesis, recombinant
expression, biochemical or enzymatic fragmentation of a larger
molecule, chemical cleavage of larger molecule, a combination of
the foregoing or, in general, made by any other method in the art,
and preferably isolated.
[0066] Binding peptides useful in the presently disclosed subject
matter also include peptides having one or more substitutions,
additions, and/or deletions of residues relative to the sequence of
an exemplary cell binding peptide or growth factor binding peptide
shown herein at Tables 1-5, as long as the binding properties of
the exemplary binding peptides to their targets are substantially
retained. Thus, the binding peptides include those that differ from
the exemplary sequences by about 1, 2, 3, 4, 5, 6, 7, 8, 9, or 10
amino acids, and include binding peptides that share sequence
identity with the exemplary peptide of at least 65%, 66%, 67%, 68%,
69%, 70%, 71%, 72%, 73%, 74%, 75%, 80%, 81%, 82%, 83%, 84%, 85%,
86%, 87%, 88%, 89%, 90%, 91%, 92%, 93%, 94%, 95%, 96%, 97%, 98%,
99%, or greater sequence identity. Sequence identity can be
calculated manually or it can be calculated using a computer
implementation of a mathematical algorithm, for example, GAP,
BESTFIT, BLAST, FASTA, and TFASTA, or other programs or methods
known in the art. Alignments using these programs can be performed
using the default parameters. A binding peptide can have an amino
acid sequence consisting essentially of a sequence of an exemplary
binding peptide or a binding peptide can have one or more different
amino acid residues as a result of substituting an amino acid
residue in the sequence of the exemplary binding peptide with a
functionally similar amino acid residue (a "conservative
substitution"); provided that the peptide containing the
conservative substitution will substantially retain the binding
activity of the exemplary binding peptide not containing the
conservative substitution. Examples of conservative substitutions
include the substitution of one non-polar (hydrophobic) residue
such as alanine, isoleucine, valine, leucine, or methionine for
another; the substitution between asparagine and glutamine, the
substitution of one large aromatic residue such as tryptophan,
tyrosine, or phenylalanine for another; the substitution of one
small polar (hydrophilic) residue for another such as between
glycine, threonine, serine, and proline; the substitution of one
basic residue such as lysine, arginine, or histidine for another;
or the substitution of one acidic residue such as aspartic acid or
glutamic acid for another.
[0067] Accordingly, binding peptides useful in the presently
disclosed subject matter include those peptides that are
conservatively substituted variants of the binding peptides set
forth in SEQ ID NOs: 1-16 (cell binding peptides), SEQ ID NOs: 25,
28-33, 36 (PDGF binding peptides), and SEQ ID NOs: 40-42 (GDF
binding peptides), and those peptides that are variants having at
least 65% sequence identity or greater to the binding peptides set
forth in SEQ ID NOs: 1-16, SEQ ID NOs: 25, 28-33, 36, and SEQ ID
NOs: 40-42, wherein all of the variant binding peptides useful in
the presently disclosed subject matter substantially retain the
ability to bind to their target.
[0068] Binding peptides can include L-form amino acids, D-form
amino acids, or a combination thereof. Representative
non-genetically encoded amino acids include but are not limited to
2-aminoadipic acid; 3-aminoadipic acid; .beta.-aminopropionic acid;
2-aminobutyric acid; 4-aminobutyric acid (piperidinic acid);
6-aminocaproic acid; 2-aminoheptanoic acid; 2-aminoisobutyric acid;
3-aminoisobutyric acid; 2-aminopimelic acid; 2,4-diaminobutyric
acid; desmosine; 2,2'-diaminopimelic acid; 2,3-diaminopropionic
acid; N-ethylglycine; N-ethylasparagine; hydroxylysine;
allo-hydroxylysine; 3-hydroxyproline; 4-hydroxyproline;
isodesmosine; allo-isoleucine; N-methylglycine (sarcosine);
N-methylisoleucine; N-methylvaline; norvaline; norleucine;
ornithine; and 3-(3,4-dihydroxyphenyl)-L-alanine ("DOPA").
Representative derivatized amino acids include, for example, those
molecules in which free amino groups have been derivatized to form
amine hydrochlorides, p-toluene sulfonyl groups, carbobenzoxy
groups, t-butyloxycarbonyl groups, chloroacetyl groups or formyl
groups. Free carboxyl groups can be derivatized to form salts,
methyl and ethyl esters or other types of esters or hydrazides.
Free hydroxyl groups can be derivatized to form O-acyl or O-alkyl
derivatives. The imidazole nitrogen of histidine can be derivatized
to form N-im-benzylhistidine.
[0069] Further, a binding peptide according to the presently
disclosed subject matter can include one or more modifications,
such as by addition of chemical moieties, or substitutions,
insertions, and deletions of amino acids, where such modifications
provide for certain advantages in its use, such as to facilitate
attachment to the polymer with or without a spacer or to improve
peptide stability. The term "spacer" is used herein, for the
purposes of the specification and claims, to refer to a compound or
a chemical moiety that is optionally inserted between a binding
peptide and the polymer. In some embodiments, the spacer also
serves the function of a linker (i.e. to attach the binding peptide
to the polymer). Therefore, the terms "linker" and "spacer" can be
used interchangeably herein, for the purposes of the specification
and claims, when performing the dual functions of linking
(attaching) the peptide to the polymer and spacing the binding
peptide from the polymer. In some cases the spacer can serve to
position the binding peptide at a distance and in a spatial
position suitable for binding and capture and/or in some cases the
spacer can serve to increase the solubility of the binding peptide.
Spacers can increase flexibility and accessibility of the binding
peptide to its target, as well as increase the binding peptide
density on the polymer surface. Virtually all chemical compounds,
moieties, or groups suitable for such a function can be used as a
spacer unless adversely affecting the binding behavior to such an
extent that binding of the target to the binding peptides is
prevented or substantially impaired. Thus, the term "binding
peptide" encompasses any of a variety of forms of binding peptide
derivatives including, for example, amides, conjugates with
proteins, conjugates with polyethylene glycol or other polymers,
cyclic peptides, polymerized peptides, peptides having one or more
amino acid side chain group protected with a protecting group, and
peptides having a lysine side chain group protected with a
protecting group. Any binding peptide derivative that has
substantially retained target binding characteristics can be used
in the practice of the presently disclosed subject matter.
[0070] Further, a chemical group can be added to the N-terminal
amino acid of a binding peptide to block chemical reactivity of the
amino terminus of the peptide. Such N-terminal groups for
protecting the amino terminus of a peptide are well known in the
art, and include, but are not limited to, lower alkanoyl groups,
acyl groups, sulfonyl groups, and carbamate forming groups.
Preferred N-terminal groups can include acetyl,
9-fluorenylmethoxycarbonyl (Fmoc), and t-butoxy carbonyl (Boc). A
chemical group can be added to the C-terminal amino acid of a
synthetic binding peptide to block chemical reactivity of the
carboxy terminus of the peptide. Such C-terminal groups for
protecting the carboxy terminus of a peptide are well known in the
art, and include, but are not limited to, an ester or amide group.
Terminal modifications of a peptide are often useful to reduce
susceptibility by protease digestion, and to therefore prolong a
half-life of a binding peptide in the presence of biological fluids
where proteases can be present. In addition, as used herein, the
term "binding peptide" also encompasses a peptide wherein one or
more of the peptide bonds are replaced by pseudopeptide bonds
including but not limited to a carba bond (CH.sub.2--CH.sub.2), a
depsi bond (CO--O), a hydroxyethylene bond (CHOH--CH.sub.2), a
ketomethylene bond (CO--CH.sub.2), a methylene-oxy bond
(CH.sub.2--O), a reduced bond (CH.sub.2--NH), a thiomethylene bond
(CH.sub.2--S), an N-modified bond (--NRCO), and a thiopeptide bond
(CS--NH).
[0071] In one embodiment, the binding peptides are covalently
attached to the polymer comprised in the implantable device. In one
embodiment, the linkers/spacers for use in attaching binding
peptides to polymers have at least two chemically active groups
(functional groups), of which one group binds to the polymer, and a
second functional group binds to the binding peptide or in some
cases it binds to the "spacer" already attached to the binding
peptide. Preferably, the attachment of the binding peptides to the
polymer is effected through a spacer. Virtually all chemical
compounds, moieties, or groups suitable for such a function can be
used as a spacer unless adversely affecting the peptide binding
behavior to such an extent that binding of the target to the
binding peptides is prevented or substantially impaired.
[0072] Again, the terms "linker" and "spacer" can be used
interchangeably herein, for the purposes of the specification and
claims, when performing the dual functions of linking (attaching)
the binding peptide to the polymer and spacing the peptide from the
polymer. In many embodiments herein, the linkers used to attach the
binding peptide to the polymer function as both a linker and a
spacer. For example, a linker molecule can have a linking
functional group on either end while the central portion of the
molecule functions as a spacer. The binding peptides of the
presently disclosed subject matter can comprise a functional group
that is intrinsic to the binding peptide (e.g., amino groups on
lysine), or the functional group can be introduced into the binding
peptide by chemical modification to facilitate covalent attachment
of the binding peptide to the polymer. Similarly, the polymer can
comprise a functional group that is intrinsic to the polymer (e.g.,
amino groups on collagen), or the polymer can be modified with a
functional group to facilitate covalent attachment to the binding
peptide. The binding peptide can be covalently attached to the
polymer with or without one or more spacer molecules.
[0073] For example, linkers/spacers are known to those skilled in
the art to include, but are not limited to, chemical compounds
(e.g., chemical chains, compounds, reagents, and the like). The
linkers/spacers may include, but are not limited to,
homobifunctional linkers/spacers and heterobifunctional
linkers/spacers. Heterobifunctional linkers/spacers, well known to
those skilled in the art, contain one end having a first reactive
functionality (or chemical moiety) to specifically link a first
molecule (e.g, polymer), and an opposite end having a second
reactive functionality to specifically link to a second molecule
(e.g, binding peptide). It is evident to those skilled in the art
that a variety of bifunctional or polyfunctional reagents, both
homo- and hetero-functional can be employed as a linker/spacer with
respect to the presently disclosed subject matter such as, for
example, those described in the catalog of the PIERCE CHEMICAL CO.,
Rockford, Ill.; amino acid linkers/spacers that are typically a
short peptide of between 3 and 15 amino acids and often containing
amino acids such as glycine, and/or serine; and wide variety of
polymers including, for example, polyethylene glycol. In one
embodiment, representative linkers/spacers comprise multiple
reactive sites (e.g., polylysines, polyornithines, polycysteines,
polyglutamic acid and polyaspartic acid) or comprise substantially
inert peptide spacers (e.g., polyglycine, polyserine, polyproline,
polyalanine, and other oligopeptides comprising alanyl, serinyl,
prolinyl, or glycinyl amino acid residues). In one embodiment,
representative spacers between the reactive end groups in the
linkers include, by non-limiting example, the following functional
groups: aliphatic, alkene, alkyne, ether, thioether, amine, amide,
ester, disulfide, sulfone, and carbamate, and combinations thereof.
The length of the spacer can range from about 1 atom to 200 atoms
or more. In one embodiment, linkers/spacers comprise a combination
of one or more amino acids and another type of spacer or linker
such as, for example, a polymeric spacer.
[0074] Suitable polymeric spacers/linkers are known in the art, and
can comprise a synthetic polymer or a natural polymer.
Representative synthetic polymer linkers/spacers include but are
not limited to polyethers (e.g., poly(ethylene glycol) ("PEG"), 11
unit polyethylene glycol ("PEG10"), or 1 unit polyethylene glycol
("mini-PEG" or "MP"), poly(propylene glycol), poly(butylene
glycol), polyesters (e.g., polylactic acid (PLA) and polyglycolic
acid (PGA)), polyamines, polyamides (e.g., nylon), polyurethanes,
polymethacrylates (e.g., polymethylmethacrylate; PMMA), polyacrylic
acids, polystyrenes, and polyhexanoic acid, and combinations
thereof. Polymeric spacers/linkers can comprise a diblock polymer,
a multi-block copolymer, a comb polymer, a star polymer, a
dendritic or branched polymer, a hybrid linear-dendritic polymer, a
branched chain comprised of lysine, or a random copolymer. A
spacer/linker can also comprise a mercapto(amido)carboxylic acid,
an acrylamidocarboxylic acid, an acrlyamido-amidotriethylene
glycolic acid, 7-aminobenzoic acid, and derivatives thereof.
[0075] In one embodiment, the binding peptide comprises one or more
modifications to the peptide N-terminus, peptide C-terminus, or
within the peptide amino acid sequence, to facilitate covalent
attachment of the binding peptide to a polymer device with or
without a spacer. The binding peptides can comprise one or more
modifications including, but not limited to, addition of one or
more groups such as hydroxyl, thiol, carbonyl, carboxyl, ester,
carbamate, hydrazide, hydrazine, isocyanate, isothiocyanate, amino,
alkene, dienes, maleimide, .alpha.,.beta.-unsaturated carbonyl,
alkyl halide, azide, epoxide, N-hydroxysuccinimide (NHS) ester,
lysine, or cysteine. In addition, a binding peptide can comprise
one or more amino acids that have been modified to contain one or
more chemical groups (e.g., reactive functionalities such as
fluorine, bromine, or iodine) to facilitate linking the binding
peptide to a spacer molecule or to the substrate to which the
binding peptide will be attached.
[0076] The binding peptides can be covalently attached to the
substrate through one or more anchoring (or linking) groups on the
substrate and the binding peptide. The binding peptides of the
presently disclosed subject matter can comprise a functional group
that is intrinsic to the binding peptide, or the binding peptide
can be modified with a functional group to facilitate covalent
attachment to the substrate with or without a spacer.
Representative anchoring (or linking) groups include by
non-limiting example hydroxyl, thiol, carbonyl, carboxyl, ester,
carbamate, hydrazide, hydrazine, isocyanate, isothiocyanate, amino,
alkene, dienes, maleimide, .alpha.,.beta.-unsaturated carbonyl,
alkyl halide, azide, epoxide, NHS ester, lysine, and cysteine
groups on the surface of the substrate. The anchoring (or linking)
groups can be intrinsic to the material of the substrate (e.g.,
amino groups on a collagen or on a polyamine-containing polymer) or
the anchoring groups can be introduced into the substrate by
chemical modification.
[0077] By way of non-limiting example, in one embodiment, a binding
peptide is attached to a substrate in a two step process (see FIG.
1; Mikulec & Puleo, 1996, J. Biomed. Mat. Res., Vol 32,
203-08). In the first step, the anchoring (or linking) groups
(i.e., amino groups on a collagen for example) on the surface of a
substrate are activated by an acylating reagent (4-nitrophenyl
chloroformate). In the second step, a lysine residue which has been
introduced along with a PEG10 spacer at the C-terminus of a binding
peptide is reacted with the activated chloroformate intermediate on
the substrate surface, resulting in attachment of the binding
peptide to the substrate.
[0078] By way of non-limiting example, in one embodiment, a binding
peptide is covalently attached to a substrate comprising an amino
functional group (see FIG. 2). FIG. 2 exemplifies attachment of a
binding peptide comprising an aldehyde group at one terminus to a
substrate that comprises an amino functional group. The binding
peptide comprising an aldehyde functional group is treated with the
substrate amino groups under reductive amination conditions to give
attached binding peptide. In another embodiment not depicted in
FIG. 2, a binding peptide comprising an amine functional group is
reacted with the substrate amino groups via a homobifunctional
linker such as, for example, glutaraldehyde, to yield a covalently
attached binding peptide (Simionescu et. al., 1991, J. Biomed
Mater. Res., 25:1495-505).
[0079] By way of non-limiting example, in one embodiment, a
homobifunctional linker possessing N-hydroxysuccinimide esters at
both ends is reacted at one end with the binding peptide having an
amino group (FIG. 3). The binding peptide with attached linking
group is then reacted through the remaining N-hydroxysuccinimide
ester with an amino group on the substrate to form a
peptide-substrate conjugate (FIG. 3). The homobifunctional
N-hydroxysuccinimide ester depicted in FIG. 3 is BS.sup.3
crosslinking reagent (THERMO SCIENTIFIC, Rockford, Ill.). As stated
herein previously, the length and type of spacer groups between the
two reactive end groups on the NHS ester can vary.
[0080] By way of non-limiting example, in one embodiment, a binding
peptide is covalently attached to a substrate having amino
functional groups in a two-step process using a disulfide linkage
(see FIG. 4; Hermanson, G. T. Bioconjugate Techniques; Academic
Press: San Diego, 1996; pp. 150-151). First, the substrate
containing amino groups is reacted with 2-iminothiolane resulting
in the introduction of thiol groups on the substrate. Simultaneous
addition of 4,4'-dithiodipyridine or 6,6'-dithiodinicotinic acid
results in rapid capping of the newly-introduced thiol as a pyridyl
disulfide. Second, the binding peptide containing a free thiol is
attached covalently to the substrate through a thiol-disulfide
exchange resulting in a disulfide bond between the substrate and
binding peptide.
[0081] By way of non-limiting example, in one embodiment, a binding
peptide is attached covalently to a substrate comprising amino
functional groups in a similar process using a disulfide linkage
(see FIG. 5; Carlsson et al., 1978, Biochem. J., 173:723-37). The
substrate is first functionalized with amine groups using known
methods (if the amino groups are not intrinsic to the material of
the substrate). Next, a thiol-cleavable, heterobifunctional (amine-
and sulfhydryl-reactive) compound (LC-SPDP; THERMO SCIENTIFIC,
Rockford, Ill.) is reacted with the amino-functionalized substrate.
The binding peptide is reacted with the LC-SPDP modified
substrate.
[0082] By way of non-limiting example, in one embodiment, a binding
peptide is attached covalently to a substrate via a thioether bond
formed by reaction of a thiol and maleimide (O'Sullivan et al.,
1979, Anal. Biochem., 100:100-8). In one embodiment, the maleimide
is added to a substrate comprising amino functional groups and then
the modified substrate is reacted with a binding peptide having a
free thiol group. Alternatively, in one embodiment, the same
chemical scheme is utilized but with the substrate modified with a
thiol group and the binding peptide modified with the maleimido
group.
[0083] By way of non-limiting example, in one embodiment, a binding
peptide is covalently attached through a non-backbone anhydride
group of a polyanhydride polymer, polymaleic acid (PMA), through a
reactive lysine group on the binding peptide shown in the schematic
diagram in FIG. 6 (Pompe, et al., 2003, Biomacromolecules,
4(4):1072-9).
[0084] By way of non-limiting example, in one embodiment, a binding
peptide is covalently attached to a chitosan. The chemical scheme
is shown in FIG. 7. First, the amino group on chitosan is protected
with phthaloyl group. The hydroxyl group on chitosan is then
reacted with chloroacetic acid to give an acid handle on chitosan.
The binding peptide amine is coupled to the acid group on the
chitosan to give the binding peptide-chitosan conjugate. The
phthaloyl group is then removed using hydrazine.
[0085] By way of non-limiting example, in one embodiment a binding
peptide is covalently attached to a chitosan. The chemical scheme
is shown in FIG. 8. First, the amino group on chitosan is protected
with a phthaloyl group. The hydroxyl group on chitosan is then
converted to a bromo group under standard halogenation conditions.
The binding peptide amine is reacted with halogenated chitosan to
give the binding peptide-chitosan conjugate. The phthaloyl group is
finally removed by reacting with hydrazine.
[0086] By way of non-limiting example, in one embodiment a binding
peptide is covalently attached to chitosan through the amino group
on chitosan. For example, a chemical scheme using a
homobifunctional N-hydroxysuccinimide ester, such as that described
for FIG. 3, is useful for attaching the binding peptide through the
amino group on chitosan.
[0087] By way of non-limiting example, in one embodiment a binding
peptide is covalently attached to a hyaluronan (HA). The chemical
scheme is shown in FIG. 9. The hyaluronan is chemically modified at
the carboxylic acid group on the glucuronate units. The carboxylic
group is activated using carbonyl diimidazole (CD). The activated
HA is then reacted with the amino group of binding peptide to yield
the peptide-HA conjugate.
[0088] By way of non-limiting example, in one embodiment, a binding
peptide is covalently attached to a hyaluronan (HA). The chemical
scheme is shown in FIG. 10. Hyaluronan is chemically modified at
the carboxylic acid group on the glucuronate units. The carboxylic
group is activated using water soluble carbodiimide such as
1-ethyl-3-(3-dimethylaminopropyl) carbodimide (EDC) along with
HOBt. The activated HA is coupled with the amino group of a binding
peptide to yield the peptide-HA conjugate.
[0089] By way of non-limiting example, in one embodiment, a binding
peptide is covalently attached to cellulose. The chemical scheme is
shown in FIG. 11. Hydroxyl groups on the polysaccharide are first
reacted with epichlorohydrin to introduce an epoxide. Ring opening
of the epoxide by reaction with aqueous ammonia provides free amino
groups that can function as anchors for peptide conjugation using
chemistry described in previous embodiments (Matsumoto, et al.
(1980) J. Biochem., 87: 535-540).
[0090] By way of non-limiting example, in one embodiment, a binding
peptide is covalently attached to oxidized cellulose. The chemical
scheme is shown in FIG. 12. Sulfhydryl groups are introduced by
reaction of carboxylates on the oxidized cellulose with cystamine
and EDC followed by reduction with dithiothreitol (DTT). Activation
of sulfhydryls with 6,6'-dithiodinicotinic acid (DTNA) followed by
a sulfhydryl-containing binding peptide results in covalent
attachment of the peptide to the oxidized cellulose through a
disulfide bond. In another embodiment not depicted in FIG. 12, the
sulfhydryl modified oxidized cellulose is reacted with a maleimide
or other Michael acceptor on the binding peptide resulting in
covalent attachment through a thioether bond. In another embodiment
not depicted in FIG. 12, carboxyl groups on oxidized cellulose are
activated with EDC and 1-hydroxybenzotriazole (HOBt) followed by
reaction with cell binding peptide containing a free amine group.
This results in conjugation of peptide to the oxidized cellulose
through an amide bond (this chemistry is exemplified in FIG. 10).
In another embodiment not depicted in FIG. 12, a cell binding
peptide can be covalently attached to oxidized cellulose through
the aldehyde groups on the oxidized cellulose. In this example, a
cell binding peptide having a free amine undergoes reductive
amination with the aldehyde group on the polymer substrate to yield
an amine bond as shown in FIG. 2 (the chemistry is the same as that
in FIG. 2 except that the functional groups on the polymer
substrate and cell binding peptide are reversed).
[0091] By way of non-limiting example, in one embodiment, a cell
binding peptide can be covalently attached to an oxidized dextran
polymer substrate by reductive amination as described above for
oxidized cellulose. More specifically, a cell binding peptide
having a free amine undergoes reductive amination with the aldehyde
group on the polymer substrate to yield an amine bond as shown in
FIG. 2 (the chemistry is the same as that in FIG. 2 except that the
functional groups on the polymer substrate and cell binding peptide
are reversed).
[0092] By way of non-limiting example, in one embodiment, more than
one binding peptide is attached to a substrate. Attaching multiple
binding peptides to a single substrate is only limited by practical
considerations related to the method of attachment. For example, in
one embodiment, two different binding peptides are covalently
attached to a substrate using any of the chemical schemes shown in
FIGS. 1-12. In each of the chemical schemes depicted in FIGS. 1-12,
the substrate having a functional group is reacted with two or more
different binding peptides that each comprise a functional group to
covalently attach the two or more binding peptides to the substrate
based on simple competition between the binding peptides. In
particular, for example, in the case of the chemical schemes
depicted in FIGS. 1 and 2, the modified substrate is reacted with
two or more different binding peptides that each comprise an amino
group or an aldehyde group (i.e., the two different binding
peptides replace the single peptide depicted in FIGS. 1 and 2), to
covalently attach the two or more binding peptides to the substrate
through the amino or aldehyde group, respectively. In the case of
the chemical schemes depicted in FIGS. 4 and 5, the modified
substrate is reacted with two or more different binding peptides
that each comprise a thiol group, to covalently attach the two or
more binding peptides to the substrate through the thiol group
(i.e., the "HS-Peptide" in FIGS. 4 and 5 in this embodiment
represents two or more different binding peptides).
[0093] By way of non-limiting example, in one embodiment, two
different binding peptides are covalently attached to a substrate
comprising amino groups using the chemical scheme shown in FIG. 13.
In this embodiment, the amino groups on the substrate are modified
with maleimido groups. The modified substrate is then reacted with
a binding peptide comprising both a thiol group and an aldehyde
group to covalently attach the binding peptide to the substrate
through the thiol group. Next, the substrate-binding peptide
conjugate is reacted with another binding peptide having a
hydrazine group, to give a second covalent bond through the
aldehyde-hydrazine (see FIG. 13). Alternatively, in one embodiment,
the same chemical scheme is utilized but with the substrate
modified with a thiol group and the binding peptide modified with
the maleimido group. In addition to using this scheme to covalently
attach different binding peptides, the scheme is also useful for
attaching the same binding peptide.
[0094] In one embodiment, the presently disclosed subject matter
provides cell binding peptides. In one embodiment, the cell binding
peptides comprise a sequence selected from the group consisting of
SEQ ID NOs: 1-20. In one embodiment, the cell binding peptides
comprise a sequence selected from the group consisting of SEQ ID
NOs: 1-16, conservatively substituted variants of SEQ ID NOs: 1-16,
and variants having at least 70% sequence identity to SEQ ID NOs:
1-16, wherein the variant cell binding peptide substantially
retains the ability to bind cells consisting of SEQ ID NOs: 1-20.
The cell binding peptides bind to one or more of fibroblasts,
endothelial cells, or stem cells.
[0095] In one embodiment, the presently disclosed subject matter
provides platelet derived growth factor (PDGF) binding peptides. In
one embodiment, the PDGF peptides comprise a sequence selected from
the group consisting of SEQ ID NOs: 25, 28-33, 36, 38, 39, and
peptide sequence motifs #1-5; conservatively substituted variants
of SEQ ID NOs: 25, 28-33, 36; and variants having at least 70%
sequence identity to SEQ ID NOs: 25, 28-33, 36; wherein the variant
PDGF binding peptide substantially retains the ability to bind
PDGF.
[0096] In one embodiment, the presently disclosed subject matter
provides growth differentiation factor (GDF) binding peptides
previously published in US Patent Application Publication No. US
2009/0098175 A1 comprising a sequence set forth in SEQ ID NOs:
40-43, conservatively substituted variants of SEQ ID NOs: 40-42,
variants having at least 70% sequence identity to SEQ ID NOs:
40-42, wherein the variant GDF binding peptide substantially
retains the ability to bind GDF.
[0097] In one embodiment, the binding peptides comprise one or more
modifications to the N-terminus, peptide C-terminus, or within the
peptide amino acid sequence. In one embodiment the modification is
selected from the group consisting of aldehyde group, hydroxyl
group, thiol group, amino group, amino acids, lysine, cysteine,
acetyl group, polymers, synthetic polymers, polyethers,
poly(ethylene glycol) ("PEG"), an 11 unit polyethylene glycol
("PEG10"), and a 1 unit polyethylene glycol ("mini-PEG" or "MP"),
and combinations thereof.
[0098] In one embodiment, the presently disclosed subject matter
provides an implantable device for tissue repair comprising a
polymer having a covalently attached binding peptide. In one
embodiment, the binding peptide is a cell binding peptide that
binds one or more of stem cells, fibroblasts, or endothelia cells.
In one embodiment the binding peptide is a cell binding peptide and
one or more growth factor binding peptides. In one embodiment, the
binding peptide is a growth factor binding peptide. In one
embodiment, the growth factor binding peptide is a PDGF binding
peptide or a GDF binding peptide. In one embodiment, the tissue for
repair comprises any one or more of tendon, muscle, connective
tissue, ligament, cardiac tissue, vascular tissue, or dermis.
[0099] In one embodiment, the implantable device comprising the
polymer is selected from the group consisting of a gel, a hydrogel,
an injectable material, an extracellular matrix, a decellularized
tissue, a dermal matrix, an acellular human dermis, an acellular
porcine dermis, an acellular bovine dermis, a porcine small
intestinal submucosa (SIS), an acellular myocardium, a cardiac
patch, a decellularized vascular conduit, a surgical mesh, a skin
graft, a dural graft, a graft for foot ulcer repair, a hernia
repair graft, a graft for abdominal repair, a tendon wrap, a tendon
augmentation graft, a graft for rotator cuff repair, a graft or
mesh for breast reconstruction, a composite surgical mesh
comprising a synthetic polymer and a biopolymer, and derivatives
and combinations thereof. In one embodiment, the polymer is a
biopolymer selected from the group consisting of a collagen, an
injectable collagen, a keratin, a silk, a polysaccharide, a
dextran, an agarose, a cellulose derivative, an oxidized cellulose,
an oxidized regenerated cellulose, a carboxymethylcellulose, a
hydroxypropylmethylcellulose, a chitosan, a chitin, a hyaluronic
acid, and derivatives and combinations thereof. In one embodiment,
the polymer is a synthetic polymer selected from the group
consisting of polymaleic anhydride having molecular weight of about
5,000 Dalton or less and a block co-polymer of polymaleic anhydride
having molecular weight of about 5,000 Dalton or less and a
co-polymer comprising a biodegradable functionality, wherein the
co-polymer is selected from the group consisting of polylactic
acid, polyglycolic acid, polylactic-co-glycolic acid,
polycaprolactone, poly-3-hydroxybutyrate, poly(p-dioxanone) and
copolymers thereof, polyhydroxyalkanoate, poly(propylene fumarate),
poly(ortho esters), and polyanhydrides, and combinations thereof.
In one embodiment, the binding peptide is attached to the polymer
with or without a spacer.
[0100] In one embodiment, the presently disclosed subject matter
provides a method for tissue repair comprising delivering to a
subject an implantable device for tissue repair, wherein the
implantable device comprises a polymer having a covalently attached
binding peptide, wherein the implantable device serves as a
scaffold for tissue repair. In one embodiment, the tissue for
repair comprises any one or more of tendon, muscle, connective
tissue, ligament, cardiac tissue, vascular tissue, or dermis. In
one embodiment, the binding peptide is a cell binding peptide that
binds one or more of stem cells, fibroblasts, or endothelial cells.
In one embodiment the binding peptide is a cell binding peptide and
one or more growth factor binding peptides. In one embodiment, the
binding peptide is a growth factor binding peptide. In one
embodiment, the growth factor binding peptide is a PDGF binding
peptide or a GDF binding peptide.
[0101] In one embodiment, the presently disclosed subject matter
provides a method for capturing cells onto an implantable device
for tissue repair comprising contacting a sample comprising cells
with the implantable device, wherein the implantable device
comprises a polymer having a covalently attached cell binding
peptide, and wherein the cells comprised in the sample are captured
onto the implantable device through binding to the attached cell
binding peptide. In one embodiment, the binding peptide is a cell
binding peptide that binds one or more of stem cells, fibroblasts,
or endothelia cells. In one embodiment, the sample comprising cells
comprises allogeneic stem cells, bone marrow, adipose tissue,
stromal vascular fraction of adipose tissue, blood, blood products,
platelets, platelet-rich plasma (PRP), umbilical cord blood,
embryonic tissues, placenta, amniotic epithelial cells, tissue
punch, omentum, recombinant GDF, recombinant PDGF, or a homogeneous
or heterogeneous population of cultured cells, or combinations or
derivatives thereof. In one embodiment, the polymer further
comprises an attached growth factor binding peptide and the sample
comprising cells comprises a growth factor, wherein the growth
factor comprised in the sample is captured onto the implantable
device through binding to the attached growth factor binding
peptide.
[0102] A method for tissue repair comprising contacting a sample
comprising cells with an implantable device comprising a polymer
having a covalently attached cell binding peptide, wherein the
cells comprised in the sample are captured onto the implantable
device through binding to the attached cell binding peptide, and
delivering to a subject the implantable device for tissue repair.
In one embodiment, the tissue for repair comprises any one or more
of tendon, muscle, connective tissue, ligament, cardiac tissue,
vascular tissue, or dermis. In one embodiment, the cell binding
peptide binds one or more of stem cells, fibroblasts, or endothelia
cells. In one embodiment, the sample comprising cells comprises
bone marrow, allogeneic stem cells, adipose tissue, stromal
vascular fraction of adipose tissue, blood, blood products,
platelets, platelet-rich plasma (PRP), umbilical cord blood,
embryonic tissues, placenta, amniotic epithelial cells, tissue
punch, omentum, recombinant GDF, recombinant PDGF, or a homogeneous
or heterogeneous population of cultured cells, or combinations or
derivatives thereof. In one embodiment, the polymer further
comprises an attached growth factor binding peptide and the sample
comprising cells comprises a growth factor, wherein the growth
factor comprised in the sample is captured onto the implantable
device through binding to the attached growth factor binding
peptide.
[0103] A method for capturing growth factors onto an implantable
device for tissue repair comprising contacting a sample comprising
growth factors with the implantable device, wherein the implantable
device comprises a polymer having one or more covalently attached
growth factor binding peptides, wherein the growth factor binding
peptide is a PDGF binding peptide or a GDF binding peptide, and
wherein the growth factor comprised in the sample is captured onto
the implantable device through binding to the attached growth
factor binding peptide. In one embodiment, the sample comprising
growth factor comprises bone marrow, allogeneic stem cells, adipose
tissue, stromal vascular fraction of adipose tissue, blood, blood
products, platelets, platelet-rich plasma (PRP), umbilical cord
blood, embryonic tissues, placenta, amniotic epithelial cells,
tissue punch, omentum, recombinant GDF, recombinant PDGF, or a
homogeneous or heterogeneous population of cultured cells, or
combinations or derivatives thereof.
[0104] A method for tissue repair comprising contacting a sample
comprising growth factor with an implantable device comprising a
polymer having one or more covalently attached growth factor
binding peptides, wherein the growth factor binding peptide is a
PDGF binding peptide or a GDF binding peptide, wherein the growth
factor comprised in the sample is captured onto the implantable
device through binding to the attached growth factor binding
peptide, and delivering to a subject the implantable device for
tissue repair. In one embodiment, the tissue for repair comprises
any one or more of tendon, muscle, connective tissue, ligament,
cardiac tissue, vascular tissue, or dermis. In one embodiment, the
sample comprising growth factor comprises bone marrow, allogeneic
stem cells, adipose tissue, stromal vascular fraction of adipose
tissue, blood, blood products, platelets, platelet-rich plasma
(PRP), umbilical cord blood, embryonic tissues, placenta, amniotic
epithelial cells, tissue punch, omentum, recombinant GDF,
recombinant PDGF, or a homogeneous or heterogeneous population of
cultured cells, or combinations or derivatives thereof.
[0105] The following examples are provided to further describe
certain aspects of the presently disclosed subject matter and are
not intended to limit the scope of the presently disclosed subject
matter.
EXAMPLES
Example 1
Identification of Cell Binding Peptides by Phage Display
[0106] Peptides that bind human mesenchymal stem cells (MSCs) were
identified by phage display biopanning. MSCs were culture amplified
from plated bone marrow aspirate (LONZA, <4 passages). After
biopanning, individual plaques were picked, grown overnight, and
tested for MSC binding activity using flow cytometry according to
the following procedure. Phage supernatant was incubated with MSCs
for 30 min on ice. Cells were washed twice with Dulbecco's
Phosphate Buffered Saline (DPBS) containing 2% FBS, then incubated
with 50 ul of anti-M13 antibody labeled with the fluorophore
phycoerythrin (PE). After 30 minutes on ice, cells were washed
twice with DPBS containing 2% FBS and binding data acquired on a BD
FACSARRAY flow cytometer. For the phage displaying MSC binding
activity, DNA sequences were analyzed and translated into peptide
sequences using Vector NTI DNA Analysis software (see FIG. 14 and
Table 1; SEQ ID NOs: 1-15).
TABLE-US-00001 TABLE 1 Stem Cell Binding Peptides SEQ ID NO: Amino
acid sequence (single letter code) 1 SSMYFSPLHTWQSAPSTSGAE 2
SSFRFQRLEDWNYPSNTDNAE 3 SSGYMQFGHLLDWTGSPSGSR 4 SSFWDVCQGDGTCYGGGSR
5 VANPFTYLSAWSNPL 6 ETLIFSKLGQWGNSLS 7 GYMQFGHLLDWTGSP 8
SVYRFDSLTTWSSNQ 9 GSWSFGTLGPWSSSQ 10 WLGNFNALTDWPTDS 11
TSGFFGSLDTWPPTL 12 NYWNFGPLEDYS 13 SVLHFHPMKSYD 14 NSIYFSPLRDYQ 15
GHFEYGRLQSIL
[0107] In addition to the cell binding sequences in Table 1 above,
a consensus stem cell binding sequence was designed based on the
sequences for the stem cell binders shown in FIG. 14.
[0108] Specifically, the following sequence: SSFRFGPLGTWNYPSTDNAE
(SEQ ID NO: 16) was designed based on sequences in FIG. 14 (SEQ ID
NOs: 5-15) which showed a high level of stem cell binding activity,
and the observation that non-binding sequences contain a larger
number of negatively charged residues in the amino and carboxyl
terminal regions, and a larger number of positively charged
residues in the central region, than the sequences showing stem
cell binding activity.
[0109] In addition to consensus cell binding sequence (SEQ ID NO:
16), the following sequence motifs SEQ ID NOs: 17-18 were generated
based on the stem cell binding activity observed for the peptide
sequences in Table 1 and FIG. 14:
TABLE-US-00002 SEQ ID NO: 17:
X.sub.1X.sub.2FX.sub.4X.sub.5LX.sub.7X.sub.8WX.sub.10X.sub.11X.sub.12X.su-
b.13X.sub.14,
wherein "X.sub.1" is F, M, L, Y, W, or N; wherein "X.sub.2" is R,
Q, P, I, Y or S; wherein "X.sub.4" is G, S, Q, T, or D; wherein
"X.sub.5" is P, R, Y, K, H, or S; wherein "X.sub.7" is G, H, E, S,
L, or T; wherein "X.sub.8" is T, D, A, Q, or P; wherein "X.sub.10"
is N, Q, S, G, or T; wherein "X.sub.11" is Y, S, N, or G; wherein
"X.sub.12" is P, A, S, or N; wherein "X.sub.13" is S, P, L, or Q;
and wherein "X.sub.14" is T, S, or N.
TABLE-US-00003 SEQ ID NO: 18:
X.sub.1X.sub.2X.sub.3X.sub.4X.sub.5X.sub.6X.sub.7X.sub.8X.sub.9X.sub.10X.-
sub.11X.sub.12X.sub.13X.sub.14,
wherein "X.sub.1" is F, W, L, Y, M, or I; wherein "X.sub.2" is N,
Y, R, P, Q, I, F, or E; wherein "X.sub.3" is F or Y; wherein
"X.sub.4" is G, S, T, Q, N, H, or D; wherein "X.sub.5" P, R, Y, T,
S, K, H, or A; wherein "X.sub.6" is L or M; wherein "X.sub.7" is T,
G, E, S, R, Q, L, K, H, or D; wherein "X.sub.8" is D, T, S, Q, P,
or A; wherein "X.sub.9" is W, Y, or I; wherein "X.sub.10" is P, N,
Q, S, G, L, D, or T; wherein "X.sub.11" is Y, S, N, T, P, or G;
wherein "X.sub.12" is P, A, S, T, D, or N; wherein "X.sub.13" is S,
P, L, or Q; and wherein "X.sub.14" is S or N.
[0110] Mutagenesis of Cell Binding Peptide Sequence SEQ ID NO: 4. A
focused phage display library was generated around the SEQ ID NO: 4
sequence with each nucleotide position varying in identity at a
ratio of 91:3:3:3, with the original nucleotide being the dominant
form. This is considered a form of "light" mutagenesis, retaining
the majority of residue identities with a few amino acid identity
changes. The construction of this "degenerate" phage library was
performed according to the methods described in Kay et al., 1996.
Individual phage were picked from the degenerate phage library and
binding to MSCs was assessed by flow cytometry as described herein
above. Forty eight phage "binders" (binding comparable to wild type
SEQ ID NO: 4) and 48 phage "non-binders" (phage binding reduced to
level of a control without a polypeptide insert) were re-amplified,
retested, and submitted for DNA sequencing to determine the insert
amino acid sequences.
[0111] Based on these results, the following first cell binding
sequence motif was generated:
TABLE-US-00004 SEQ ID NO: 19:
X.sub.1-Z.sub.2-Z.sub.3-X.sub.4-X.sub.5-C-X.sub.7-X.sub.8-X.sub.9-G-T-C-X-
.sub.13-G-G-G,
wherein "X.sub.1" is S, N, T, I, V, or G; wherein "Z.sub.2" and
"Z.sub.3" are F, W, or Y; wherein "X.sub.4" is D, E, W, N, Q, or G;
wherein "X.sub.5" is V, M, or A; wherein "X.sub.7" is Q, P, E, L,
H, R, or A; wherein "X.sub.8" is G, A, V, or R; wherein "X.sub.9"
is D, N, or E; and wherein "X.sub.13" is Y, W, or H.
[0112] Further, based on these results, the following second cell
binding sequence motif was generated:
TABLE-US-00005 SEQ ID NO: 20:
X.sub.1-X.sub.2-W-X.sub.4-X.sub.5-C-X.sub.7-X.sub.8-X.sub.9-G-T-C-X.sub.1-
3-G-G-G,
[0113] wherein "X.sub.1" is S, N, T, I, V, or G; wherein "X.sub.2"
is F or Y; wherein "X.sub.4" is D, E, W, N, Q, or G; wherein
"X.sub.5" is V, M, or A; wherein "X.sub.7" is Q, P, E, L, H, R, or
A; wherein "X.sub.8" is G, A, V, or R; wherein "X.sub.9" is D, N,
or E; and wherein "X.sub.13" is Y, W, or H.
Example 2
Generation of Synthetic Binding Peptides
[0114] Peptide Synthesis. Binding peptide sequences were
synthesized using standard solid-phase peptide synthesis techniques
on a SYMPHONY Peptide Synthesizer (PROTEIN TECHNOLOGIES, Tucson,
Ariz.) using standard Fmoc chemistry (HBTU/HOBT activation, 20%
piperidine in DMF for Fmoc removal). N-.alpha.-Fmoc-amino acids
(with orthogonal side chain protecting groups; NOVABIOCHEM). After
all residues were coupled, simultaneous cleavage and side chain
deprotection was achieved by treatment with a trifluoroacetic acid
(TFA) cocktail. Crude peptide was precipitated with cold diethyl
ether and purified by high-performance liquid chromatography on a
WATERS Analytical/Semi-preparative HPLC unit on VYDAC C18 silica
column (preparative 10 .mu.m, 250 mm.times.22 mm) using a linear
gradient of water/acetonitrile containing 0.1% TFA. Homogeneity of
the synthetic peptides was evaluated by analytical RP-HPLC (VYDAC
C18 silica column, 10 .mu.m, 250 mm.times.4.6 mm) and the identity
of the peptides confirmed with MALDI-TOF-MS. Biotinylated peptides
were generated similarly, with a GSSGK(biotin) sequence or other
spacer group added to the C-terminus of the peptide.
Example 3
Cell Binding Peptide Specificity
[0115] The synthetic biotinylated cell binding peptide SEQ ID NO: 4
was examined for its ability to specifically bind MSCs compared to
a number of other cells types including adipose-derived mesenchymal
stem cells (ASCs), dermal fibroblasts, rodent MSCs, red blood
cells, monocytes, lymphocytes and granulocytes. The cell binding
peptide was biotinylated as described herein at Example 2. Cultured
cells of each type were either purchased (ASCs and dermal
fibroblasts) or isolated from rodent bone marrow (rodent MSCs) or
human blood. Cells were first harvested and resuspended at
10.sup.6/mL in PBS+2% fetal bovine serum (FBS). An aliquot of cells
(50 .mu.L) was incubated in 50 .mu.L of peptide solution (25 .mu.M
in PBS+FBS) for 30 min at 4.degree. C. Cells were then washed twice
in PBS+FBS with 300.times.g centrifugation for 5 min between
washes. Fluorescently-tagged neutravidin (Neutravidin-PE from
INVITROGEN) was then added to the cells to label biotinylated
peptide bound to cells. Neutravidin-PE was diluted 1:250 from stock
and applied at 50 .mu.L to cells. Cells were then washed in
PBS+FBS, and acquired on a BD FACSARRAY. Peptide reactivity was
then measured as percent positivity relative to Neutravidin-PE
staining without the addition of biotinylated peptide. Cell binding
peptide SEQ ID NO: 4 was observed to have high binding to human
MSCs, human ASCs and dermal fibroblasts (see FIG. 15).
[0116] The synthetic biotinylated binding peptide SEQ ID NO: 4 was
further examined for its ability to bind endothelial cells compared
to other cell types (see FIG. 16). Biotinylated cell binding
peptide SEQ ID NO: 4 (10 .mu.M) was incubated with 25,000 cultured
cells (human umbilical vein endothelial cells (HUVECs), endothelial
colony forming cells (ECFCs; LONZA), umbilical artery smooth muscle
cells (UASMCs) or whole blood cells from freshly collected human
blood for 30 min at 4.degree. C. Cells were washed twice and
cell-bound peptide was detected with Neutravidin-PE (INVITROGEN)
for 30 min at 4.degree. C. Cells were then washed, resuspended and
fixed in 2% paraformaldehyde, and acquired on a BD FACSARRAY. The
data in FIGS. 16A & 16B show that SEQ ID NO: 4 cross-reacted
strongly with ECFCs and HUVECs, weakly with UASMCs, and had no
cross-reactivity with peripheral blood cells. ECFCs are clonally
expanded cells isolated from human umbilical cord blood, and are
considered highly proliferative endothelial progenitor cells (EPCs)
based on their clonogenic and proliferative potential. In another
experiment, binding peptide SEQ ID NO: 4 was assayed for its
ability to selectively isolate endothelial cells versus smooth
muscle cells in the presence of whole blood. HUVECs or UASMCs were
incubated in the presence of medium containing 20% whole blood and
binding peptide SEQ ID NO: 4-conjugated magnetic beads (via
biotin-SA) for 30 min. The solutions containing the
bead-peptide-cell complexes were then passed through a MILTENYI LS
column in a magnetic field. The column was washed, and the
remaining peptide-bound cells were then released from the magnetic
field and counted. The data in FIG. 16C show that binding peptide
SEQ ID NO: 4 isolated 8-fold more HUVECs compared to UASMCs.
Example 4
Capture of Cultured MSCs with Cell Binding Peptide Attached to a
Substrate
[0117] In this experiment the ability of the biotinylated cell
binding peptide SEQ ID NO: 4 to capture human MSCs from a
homogeneous cultured cell population was examined. The cell binding
peptide SEQ ID NO: 4 was biotinylated as described herein at
Example 2. The cell binding peptide SEQ ID NO: 4, and a non-binding
control peptide, were added to separate 300 .mu.l volumes of
MILTENYI BIOTEC Streptavidin microbeads at a concentration of 20
.mu.M. These beads are made from iron filings, coated with a
dextran coating which is functionalized with streptavidin moieties.
Peptide was incubated with beads for 45 min on ice. The 300 .mu.l
of peptide coated microbeads were added to pre-equilibrated LS
columns outside of the magnetic field to evenly distribute the
magnetic beads throughout the columns. Columns were then placed
into a magnetic field, and excess peptide was washed away with
buffer while retaining the peptide coated microbeads. Cultured and
expanded human MSCs from bone marrow aspirate (160,000 cells;
LONZA) were added to each LS column and allowed to pass through by
gravity flow. Flowthrough was collected and cycled through the
columns 5 times, after which the columns were washed with 5 ml
buffer. Bound cells were eluted by removing columns from the
magnetic field and flushing with 5 ml buffer into 15 ml conical
tubes. The collected flowthrough with 5 ml wash and eluted cells
were spun down, resuspended in a smaller volume, and counted by
hemacytometer (see FIG. 17). The data in FIG. 17 show capture of
approximately 70% of the MSCs by the cell binding peptide SEQ ID
NO: 4 compared to only about 10% capture by the control
peptide.
Example 5
Capture of MSCs from a Mixed Cell Population with Cell Binding
Peptide Attached to a Substrate
[0118] In this experiment, biotinylated cell binding peptide, SEQ
ID NO: 16, was attached to CELLECTION magnetic beads. The
CELLECTION beads have streptavidin coupled to a magnetic particle
through a DNA linker. Three different cell types, human MSCs, IM-9,
and U937 cells were differentially labeled with CELLTRACKER dye and
mixed in a ratio such that the MSCs represented .about.4% of the
starting cell mixture (the percentage of each cell type in the
starting mixture was 38% IM9, 56% U937, and 4% MSC). The cell
binding peptide, SEQ ID NO: 16, was biotinylated as described
herein at Example 2, as was a general cell binding peptide for use
as a control peptide in the experiment. Magnetic particles with no
peptide attached, as well as magnetic beads having attached either
the cell binding peptide, SEQ ID NO: 16, or the control peptide
were tested for their ability to capture human MSCs. The starting
cell mixture was incubated with magnetic beads having either
attached peptide or no peptide, the beads were washed, and the
captured cells were released from the beads by DNase treatment. The
cells were measured by flow cytometry histograms shown in 18A-18C.
The starting cell mixture is shown in FIG. 18A. The magnetic beads
without peptide captured little or no cells (FIG. 18B). The
magnetic beads with attached cell binding peptide SEQ ID NO: 16
captured a cell population that was 96% MSCs (FIG. 18C).
Example 6
Capture of MSCs from Bone Marrow Aspirate with Cell Binding Peptide
Attached to a Substrate
[0119] This experiment was performed to examine the ability of cell
binding peptide SEQ ID NO: 4 to capture MSCs directly from bone
marrow aspirate in comparison to two separate antibodies against
the CD105 I antigen (CD105) and the MSCA-1 stem cell antigen
(MSCA-1). This experiment employed biotinylated peptides with
streptavidin-coated MILTENYI magnetic beads. The peptides were
biotinylated as described herein at Example 2. In addition to cell
binding peptide SEQ ID NO: 4, a negative control peptide that does
not bind to MSCs was included in the experiment. For the antibody
capture experiment, magnetic beads having covalently attached CD105
or MSCA-1 antibody were employed (MILTENYI). Prior to incubation
with the peptides and antibodies, bone marrow aspirate (BMA) was
mixed with 5 volumes of 10 mM ammonium chloride for 1-2 min at room
temperature to lyse red blood cells. The lysate was centrifuged for
5 min at 300.times.g and the supernatant discarded. The cell pellet
was washed with wash buffer (PBS+0.5% bovine serum albumin+0.5 mM
EDTA) and cells were resuspended in 25 mM peptide at a
concentration of 10.sup.8 per mL. For peptide binding studies, the
cell suspension was incubated with the biotinylated peptides for 30
min at 4.degree. C. to allow for binding. After incubation, cells
were spun down at 300.times.g for 5 min, and peptide solution was
aspirated. Cells were then rinsed twice with wash buffer, with
centrifugation between washes. Cells were resuspended in 80 .mu.L
of wash buffer per 10.sup.7 cells. Streptavidin-coated beads were
then added at 20 .mu.L per 80 .mu.L of cells. The following
procedure was performed for the cell binding experiment with the
CD105 and MSCA-1 antibodies. First, 20 .mu.L of magnetic beads
having attached CD105 or MSCA-1 antibody were added to 80 .mu.L of
the resuspended cells. Bead and cell mixtures were then incubated
for 20 min at 4.degree. C. The mixtures were centrifuged to pellet
the cells, and the cells were washed once to remove unbound beads.
The cell pellet was then resuspended in 1 mL of wash buffer, and
loaded into an equilibrated LS purification column attached to a
MIDIMACS separator (MILTENYI). The separator contains a magnet,
which causes the magnetic beads to adhere to the column, while
unbound materials flow through the column. Column was then washed
three times with 3 mL of wash buffer. Column was then removed from
the magnet, and cell-bound beads were eluted by flushing the column
with 5 mL of wash buffer in a clean 15 mL conical tube. The eluants
were then plated and cultured. Colony forming units (CFUs) were
counted after 14 days in culture. The results are shown in FIG. 19.
MSC capture by stem cell binding peptide SEQ ID NO: 4 is as
efficient as capture by either of the CD105 or MSCA-1 antibodies
(FIG. 19). In contrast, no MSC capture was observed with the
negative peptide control. Cells captured with this method were also
examined for immunoreactivity for a number of antigens. When
comparing stem cell binding peptide SEQ ID NO: 4 and CD105 isolated
cells, no changes were observed for immunoreactivity for a number
of antibodies including: CD29(+), CD44(+), CD73(+), CD105(+),
CD166(+), CD90(+), CD45(-), and CD34 (-). These data suggest that
stem cell binding peptide SEQ ID NO: 4 is capable of isolating an
MSC cell population that is phenotypically similar to cells
isolated by CD105 isolation.
Example 7
Covalent Attachment of Cell Binding Peptide to Collagen
Substrate
[0120] Cell binding peptide SEQ ID NO: 4 was covalently attached to
a collagen substrate using p-nitrophenyl chloroformate chemistry
(see FIG. 1). HELISTAT collagen sponge (INTEGRA LIFE SCIENCES,
Plainsboro, N.J.) was used as the collagen substrate. The cell
binding peptide SEQ ID NO: 4 was modified at the carboxyl terminus
with a PEG-10 spacer and a lysine residue.
[0121] Collagen sponge substrate modification. HELISTAT collagen
(15 sponges, 21.6 mg) was placed in a peptide reactor vessel
flushed with nitrogen. The amount of surface amines on the collagen
was estimated at .about.35 .mu.mol/g based on quantitative
ninhydrin assay. The vessel was charged with 10 mL anhydrous
acetonitrile and DIEA (50 .mu.L). Excess (100-fold)
p-nitrophenylchloroformate (35 mg, 173 .mu.mol) was added to the
vessel and flushed with nitrogen. The reaction vessel was shaken
for 4 h on a vortexer (low setting). The reaction mixture was
filtered and the sponges were washed thoroughly with 10 mL of DCM,
anhydrous (3.times.) with shaking and then dried under nitrogen.
Based on quantitative ninhydrin assay, the majority of surface
amines were consumed during this step. This was also confirmed by
hydrolyzing a collagen sponge sample with 0.1N NaOH at 22.degree.
C. for 15 min to release the nitrophenylate ions, which were
quantified spectrophotometrically at 405 nm (E=1.7.times.10.sup.4
M.sup.-1 cm.sup.-1). The collagen-pNP sponges were then reacted
directly with peptide.
[0122] Peptide coupling. Cell binding peptide SEQ ID NO: 4 (with
PEG-10-Lys modification; 4 mg) was taken in 4 mL anhydrous
acetonitrile and DMF mixture (1:1) in a polypropylene tube flushed
with nitrogen. DIEA (50 .mu.L) was added to bring the pH to
.about.9. The collagen-pNP (11 sponges; 15.8 mg) was added to the
peptide solution. The reactor was flushed with nitrogen and
vortexed overnight. The yellow reaction solution was carefully
collected and the sponges were thoroughly washed with anhydrous
acetonitrile. The washes were carefully pooled. The sponges were
flushed and dried under nitrogen. The extent of peptide loading was
determined spectrophotometrically at 405 nm by quantifying the
p-nitrophenylate ion displaced by the peptide. The peptide loading
was determined to be 28.48 .mu.mol peptide/g of collagen.
[0123] Soluble collagen substrate modification. In another
experiment, cell binding peptide SEQ ID NO: 4 was covalently
attached to a soluble collagen substrate using homobifunctional
N-hydroxysuccinimide ester, BS.sup.3 crosslinking reagent (THERMO
SCIENTIFIC, Rockford, Ill.) (the chemistry is depicted in FIG. 3).
First the peptide having a spacer and lysine residue at the
carboxyl terminus was reacted with the BS.sup.3 crosslinking
reagent and the complex purified by HPLC. An excess of BS.sup.3 was
used to minimize peptide dimerization. The activated peptide was
then added to soluble bovine, type I collagen (BD BIOSCIENCES, San
Jose, Calif.) in a phosphate buffer (pH=8) resulting in conjugation
to collagen via lysine amino groups on collagen. The reaction
resulted in 80-90% of the peptide-BS.sup.3 complexes coupled to the
collagen.
[0124] Fibrillar collagen substrate modification. In another
experiment, cell binding peptide SEQ ID NO: 4 is covalently
attached to a fibrillar collagen substrate using homobifunctional
N-hydroxysuccinimide ester, BS.sup.3 crosslinking reagent (THERMO
SCIENTIFIC, Rockford, Ill.) (the chemistry is depicted in FIG. 3).
First, the peptide having a spacer and a lysine residue at the
C-terminus is reacted with BS.sup.3, and the resulting complex is
purified by HPLC. An excess of BS.sup.3 is used to minimize peptide
dimerization. The BS.sup.3-activated peptide is conjugated to
fibrillar collagen in PBS buffer by addition of approximately 20
.mu.mol peptide per gram of matrix. After washing and freeze-drying
the material the peptide loading efficiency is evaluated, for
example, by trypsin assay. Briefly, the tissues are placed in
trypsin digestion buffer (50 mM Tris-HCl, 0.15 mM NaCl, 10 mM
CaCl.sub.2, pH 7.5) containing 10 .mu.g/mL trypsin for 18 h at
37.degree. C. resulting in cleavage of the peptide and release of a
peptide fragment into the supernatant. An HPLC assay is used to
measure the amount of peptide fragment released using a standard
curve generated from trypsin digestion of unconjugated peptide.
Example 8
Covalent Attachment of Cell Binding Peptide to Decellularized
Tissue Substrates
[0125] Acellular collagen-rich graft substrate modification. Cell
binding peptide SEQ ID NO: 4 was covalently attached to a variety
of acellular collagen-rich graft substrates including
decellularized porcine dermis as a biological cell-binding matrix
for soft tissue and abdominal wall reconstruction.
[0126] Decellularization of rat arterial tissue. One use for an
acellular artery substrate having a covalently attached cell
binding peptide is for vascular repair as there remains an unmet
need to reduce intimal hyperplasia and thrombosis in small- to
medium-caliber prosthetic vascular grafts. For example, ePTFE,
which is commonly used for small caliber arteries (.ltoreq.6 mm),
has a high incidence of failure due to intimal hyperplasia and
ongoing surface thrombogenicity (Chlupac et al., Physiol Res, 2009,
58 Suppl 2:S119-39; Zilla et al., Biomaterials, 2007, 28:5009-27).
The absence of a selectively permeable and thrombo-resistant
endothelium is the main reason for the failure of medium to
small-caliber prosthetic vascular grafts (Zhang et al., J Cell Mol
Med, 2007, 11:945-57). Ingrowth of a vascular graft from
neighboring endothelial cells (EC), and colonization of circulating
endothelial progenitor cells (EPC) have resulted in
endothelialization of vascular grafts in animal models (Zilla et
al., Biomaterials, 2007, 28:5009-27; Shi et al., Blood, 1998, p.
362-67). Successful pre-clinical studies have not translated to the
clinic in localizing these cell types to grafts to generate a
non-thrombotic surface (Walter et al., Circulation, 2002, p.
3017-24; Werner et al., Circ Res. 2003, p. e17-24; Bhattacharya et
al., in Blood, 2000, p. 581-5; Kaushal et al., in Nat. Med. 2001,
p. 1035-40; Griese et al., in Circulation, 2003, p. 2710-5).
Positive preclinical and clinical studies involving the seeding of
cells at the luminal surface of prosthetic vascular grafts prior to
implantation supports the concept that ECs and EPCs can improve
functional outcomes in vivo (Bhattacharya et al., in Blood. 2000.
p. 581-5; Deutsch et al., Surgery, 1999, 126:847-55; Meinhart et
al., in Ann Thorac Surg. 2001. p. S327-31; Zilla et al., in J Vasc
Surg. 1994. p. 540-8; Parikh, S. A. and E. R. Edelman, Adv Drug
Deliv Rev, 2000, 42:139-61). Alternatively, mobilizing EPCs from
bone marrow followed by capture of EPCs on a vascular graft
represents an exciting alternative that eliminates most of the
complications associated with cell seeding, and is currently being
explored in the clinic with bare metal stents (Aoki et al., J Am
Coll Cardiol, 2005, 45:1574-9). In animal models, small numbers of
circulating EPCs have been shown to passively attach to implanted
grafts and decrease neointima formation following vascular injury
(Walter et al., in Circulation. 2002. p. 3017-24; Werner et al., in
Circ Res. 2003. p. e17-24). Therefore, in the present experiment an
acellular artery having a covalently attached endothelial cell
binding peptide is generated as a small-caliber vascular graft to
promote ingrowth of endothelial cells onto the graft and to capture
circulating endothelial progenitor cells (EPCs) to promote
endothelialization of the graft. In this experiment, rat arteries
are isolated and decellularized using methods based on published
procedures. For example, rats are treated with heparin (100
units/kg) and the femoral arteries, approximately 2 cm in length,
are placed in sterile distilled water for about 1 h to lyse red
blood cells. The graft is washed PBS. The artery is decellularized
in saline containing 1% Triton 100.times. and 0.1% ammonium
hydroxide for about 24-48 hours at 4.degree. C. on a mechanical
rotator. If necessary, the luminal surface is exposed to shear flow
in the decellularizing buffer for about 1-3 hours to completely
remove cellular debris. Following this procedure the grafts are
placed in PBS for about 24 hours at 4.degree. C. on a mechanical
rotator, changing the buffer at least 5 times.
[0127] Peptide attachment to rat arterial tissue. In this
experiment, cell binding peptide SEQ ID NO: 4 is covalently
attached to the decellularized rat artery tissue using the BS.sup.3
reagent described herein above for peptide covalent attachment to
soluble collagen. After purification by HPLC, the peptide-BS.sup.3
complex is added to the decellularized arteries in phosphate buffer
pH 8.0 for about 24 h at 4.degree. C. on a mechanical rotator. The
arteries are washed in buffer and stored a 4.degree. C.
Approximately 20 .mu.mole peptide per gram tissue is used for the
attachment chemistry and peptide loading efficiency is evaluated by
trypsin assay. Briefly, the tissues are placed in trypsin digestion
buffer (50 mM Tris-HCl, 0.15 mM NaCl, 10 mM CaCl.sub.2, pH7.5)
containing 10 .mu.g/ml trypsin (SIGMA, MO) for about 1 h at
37.degree. C. to yield free peptide for analysis by HPLC. Peptide
concentration is determined from a standard curve generated with
unconjugated peptide.
[0128] Decellularization of porcine dermal tissue. One use for an
acellular porcine dermal graft substrate having a covalently
attached cell binding peptide is for hernia repair as there remains
an unmet need to reduce recurrence rates which can be achieved by
accelerating post-operative healing. Wound breaking strength
represents the amount of force a surgical wound can withstand
before failing, and failure occurs when there is a deficient
quantity and quality of tissue repair (Franz, M. G., Surg Clin
North Am, 2008, 88:1-15, vii). Previous studies have suggested that
wound repair integrity reaches a normal breaking strength in 30
days (Franz et al., J Surg Res, 2001, 97: 109-16; Robson, M. C.,
Surg Clin North Am, 2003, 83:557-69). Fibroblasts are responsible
for collagen synthesis and deposition and recovery of wound
breaking strength (Franz, M. G., Surg Clin North Am, 2008, 88:1-15,
vii). Two days post surgery the inflammatory response subsides and
fibroblasts infiltrate the wound, out numbering other cell types by
day 4 (Dubay, D. A. and M. G. Franz, Surg Clin North Am, 2003,
83:463-81). Wounds are increasingly challenged during the recovery
period as patients return to normal activity. The acellular
collagen-rich graft substrate having a covalently attached cell
binding peptide becomes populated with fibroblasts and vascularizes
faster than other bioprosthetics, preventing infection and leaving
a biologic repair. Reducing the recovery time by retaining
fibroblasts at the surgical site will increase healing rates and
improve repair outcomes. Porcine dermal tissue is decellularized
using methods based on reports in the literature. For example,
porcine skin is obtained from NAHUNTA PORK CENTER (Pikeville, N.C.)
and half-thickness skin grafts are harvested using a dermatome
(ROBBINS INSTRUMENTS, Chatham, N.J.). The grafts are cut in small
squares and incubated for about 2 h at 4.degree. C. in Hank's
balanced salt solution (HBSS) containing 0.25% trypsin. The
epidermal layer is peeled away and discarded and the dermal layer
is rinsed multiple times in deionized water to reduce the salt
content. To lyse cells, dermal tissues are incubated for about 1 h
at RT in 0.5% sodium dodecyl sulfate (SDS), and rinsed multiple
times in water. The tissue is incubated at RT for about 3 h in HBSS
with gentle shaking to remove SDS and washed in water on a filter
funnel. The tissue is freeze dried in a lyophilizer and stored at
4.degree. C.
[0129] Peptide attachment to porcine dermal tissue. In this
experiment, cell binding peptide SEQ ID NO: 4 is covalently
attached to the decellularized porcine dermal tissue using
homobifunctional N-hydroxysuccinimide ester, BS.sup.3 crosslinking
reagent (THERMO SCIENTIFIC, Rockford, Ill.) (the chemistry is
depicted in FIG. 3) for the attachment to soluble collagen. After
purification by HPLC, the peptide-BS.sup.3 complex is added to the
decellularized dermis in phosphate buffer pH 8.0 for about 24 h at
4.degree. C. on a mechanical rotator. The dermis is washed in
buffer for about 1-2 h changing the buffer every 30 min, freeze
dried, and stored at -20.degree. C. Approximately 20 .mu.mole
peptide per gram tissue is used for the attachment chemistry and
peptide loading efficiency is evaluated by trypsin assay. Briefly,
the tissues are placed in trypsin digestion buffer (50 mM Tris-HCl,
0.15 mM NaCl, 10 mM CaCl.sub.2, pH7.5) containing 10 .mu.g/ml
trypsin (SIGMA, MO) for about 1 h at 37.degree. C. to yield free
peptide that can be analyzed by HPLC. Peptide concentration is
determined from a standard curve generated with unconjugated
peptide.
[0130] Commercially available decellularized tissues. Cell binding
peptide SEQ ID NO: 4 was covalently attached to two commercially
available decellularized soft tissue matrices, PERMACOL (porcine
dermis from TISSUE SCIENCE LABORATORIES, Aldershot, UK) and XENFORM
(fetal bovine dermis from TEI BIOSCIENCES, Boston, Mass.) using
homobifunctional N-hydroxysuccinimide ester, BS.sup.3 crosslinking
reagent (THERMO SCIENTIFIC, Rockford, Ill.) (the chemistry is
depicted in FIG. 3). Cell binding peptide SEQ ID NO: 4 was first
modified with a spacer and lysine residue at the carboxyl terminus
and activated with the BS.sup.3 reagent. To 11 mg of decellularized
soft tissue matrix (PERMACOL or XENFORM) was added
BS.sup.3-activated cell binding peptide (1.4 mg) in phosphate
buffer (2.0 mL). The reaction mixture was agitated by shaking
overnight at 4.degree. C. followed by 3 h at room temperature. The
peptide-matrix conjugate was isolated by vacuum filtration, washed
with phosphate buffer (4.times.5 mL) and water (2.times.5 mL), and
freeze dried. The samples were then subjected to trypsin digestion
and analyzed using HPLC to estimate the amount of cell binding
peptide covalently attached to the matrix. The amount of peptide
covalently attached to the matrix ranged from 1-4 .mu.mol peptide/g
matrix.
[0131] In addition to the above experiment describing attachment of
a cell binding peptide to acellular dermal matrices through the
C-terminus of the peptide, cell binding peptide SEQ ID NO: 4 was
also attached to the acellular matrices through the N-terminal
amino group of the SEQ ID NO: 4 that also contained a C-terminal
biotin group. By attaching the biotinylated peptide, the
distribution of the peptide on the acellular dermal matrixes was
demonstrated visually as follows. Small pieces of the acellular
dermal matrix (PERMACOL or XENFORM) approximately 3 mm.times.3 mm
were incubated in TBST buffer solution (10 mM Tris-HCL, 150 mM
NaCl, 0.01% Tween-20, pH 8.0) to swell for 2 hours at room
temperature. The solution was discarded and replaced with TBST
supplemented with 0.5% bovine serum albumin (TBST/BSA). This buffer
was aspirated and replaced with a solution of 0.4 .mu.g/ml
neutravidin conjugated with horseradish peroxidase in TBST. The
acellular dermis samples were mixed in this solution for 1 h at
room temperature. The neutravidin-HRP solution was aspirated and
samples were washed by mixing in TBST/BSA for 30 min at room
temperature. This step was repeated twice more. Detection of
neutravidin-HRP bound to peptide was performed using
3-3'-diaminobenzidine and hydrogen peroxide (SIGMAFAST DAB), which
generates an insoluble brown product. The wash solution was removed
and the acellular dermal matrix samples were placed on a microscope
slide and incubated with DAB/peroxide. Color was allowed to develop
for 5 min and photographed under tungsten light. The presence of
staining on the acellular dermal matrices to which biotinylated
cell binding peptide SEQ ID NO: 4 was attached and lack of
discernable staining in the control samples indicates that the cell
binding peptide was covalently attached over the entire surface of
the acellular dermal matrices (data not shown).
Example 9
Capture of Cultured MSCs with a Cell Binding Peptide Covalently
Attached to Collagen
[0132] This experiment measured the ability of collagen sponge
having covalently attached stem cell binding peptide SEQ ID NO: 4
to capture cultured human MSCs compared to unmodified collagen
sponge. The cell binding peptide SEQ ID NO: 4 was modified at the
carboxyl terminus with a PEG-10 spacer and a lysine residue. The
modified cell binding peptide SEQ ID NO: 4 was covalently attached
to the collagen sponge as described in Example 6. For the MSC
capture experiment, human MSCs were labeled with fluorescent
CELLTRACKER Green dye. Unmodified and peptide modified HELISTAT
sponge coupons (d=5 mm, thickness=2.5 mm) were used in the
experiment. The sponge coupons were pre-wetted in PBS+2% FBS.
Sponge coupons were transferred to a suspension of human MSCs
(.about.25,000 cells in 1 ml PBS+2% FBS). The sponge coupons were
incubated with the cells for .about.3 hr at RT rotating. Images
were taken of the sponge coupons immediately after the incubation
with cells and again after a transfer to and 19 hr incubation in 1
ml PBS+2% FBS (see FIGS. 20A-20B). The images of the peptide
modified (right panel) and unmodified (left panel) sponge coupons
shown in FIGS. 20A and 20B demonstrate the significantly improved
ability of the peptide modified sponges to capture and retain MSCs.
In addition, release of MSCs from the sponges was quantified by
measuring both fluorescence and cell count following centrifugation
of the sponges to release unbound MSCs (data not shown). Further,
after the 19 hr incubation the sponge coupons were digested with
collagenase to liberate the remaining bound cells, and the cells
were similarly quantified (data not shown). For the peptide
modified sponges, approximately 10% of the MSCs were detected in
the sponge effluent following incubation with the cells, while
approximately 40% of the MSCs were detected in the sponge effluent
for the unmodified sponge coupons. Very few cells were detected in
the sponge effluent after the 19 hr incubation (1 ml PBS+2% FBS)
for either the peptide modified or unmodified sponges. However,
after collagenase digestion of the collagen sponges to liberate
bound cells, approximately 90% of the total cell count was detected
for the peptide modified sponge and approximately 60% of the total
cell count was detected for the unmodified sponge. Accordingly, the
collagen sponges covalently modified with stem cell binding peptide
SEQ ID NO: 4 captured significantly more MSCs than unmodified
sponges.
Example 10
Capture of Endothelial Cells with a Cell Binding Peptide Covalently
Attached to Collagen
[0133] This experiment measured the ability of collagen having
covalently attached cell binding peptide SEQ ID NO: 4 (demonstrated
to bind to stem cells, fibroblasts, and endothelial cells in
Example 3 to capture and retain HUVECs. FIG. 21A shows HUVEC
capture by collagen having covalently attached cell binding peptide
SEQ ID NO: 4 (generated according to Example 6 using BS.sup.3
reagent). Briefly, 96-well plates were coated with increasing
amounts of binding peptide-modified collagen over night at
4.degree. C. Unbound collagen was removed and the plates were
blocked in tris buffered saline containing 1% BSA for 1 hr at room
temperature. After washing, 10,000 HUVECs were added per well in
serum free medium for 30 min at 37.degree. C. The plates were
washed 3 times with PBS containing 2% FBS, and captured cells were
detected with CELLTITER-GLO (INVITROGEN) using a luminometer and a
standard curve. FIG. 21A shows a peptide dependent increase in cell
retention on peptide-modified collagen, with a 3-fold increase in
cell retention for the peptide-modified collagen over unmodified
collagen. The 96 well plates were coated with 25 .mu.g of collagen
and the data in FIG. 21B show that the collagen coating was similar
for all the samples shown in FIG. 21A. For FIG. 21B, the collagen
was extracted in gel loading buffer, separated by PAGE, and total
protein was stained with SIMPLYBLUE (INVITROGEN). FIG. 21C shows
evaluation of HUVEC retention by peptide-modified collagen in the
plate format. Plates with captured HUVECs were prepared as
described in FIG. 20A. After washing they were incubated with
agitation at RT for 1 hour in PBS containing 1% FBS, washed and
then retained cells were detected with CELLTITER-GLO. The graph in
FIG. 21C shows that after 1 hour with agitation in PBS containing
2% FBS, peptide-modified collagen retained 7-fold more HUVECs than
unmodified collagen.
Example 11
Cell Binding Peptide Modified-Collagen Binds Endothelial Cells
without Altering Phenotype
[0134] Once immobilized on a vascular graft, endothelial cells must
retain their characteristic properties of promoting
endothelialization. Therefore, the phenotype, viability, and
anti-thrombogenic protein expression profiles were evaluated for
endothelial cells in the presence of collagen modified with the
endothelial cell binding peptide SEQ ID NO: 4 (generated according
to Example 7 using BS.sup.3 reagent). Cells cultured in the
presence of peptide-modified collagen, collagen with free peptide
or collagen alone for 24 hours maintained their endothelial cell
phenotype and their ability to secrete anti-thrombogenic proteins.
Specifically, HUVECs were plated on SEQ ID NO: 4 peptide-modified
collagen, collagen with 10 .mu.M free SEQ ID NO: 4 peptide or
collagen alone for 24 hours. Flow cytometry was performed using a
BD FACSARRAY, and ELISAs were performed according to manufacturers
instructions. (FIGS. 22A & 22B). Tissue-type Plasminogen
Activator (t-PA) and 6-keto Prostaglandin F1a protein expression
levels secreted in this assay are aligned with other reports on
cultured HUVECS (Kimura and Yokoi-Hayashi, Biochim Biophys Acta,
1996, 1310:1-4; Merhi-Soussi et al., J Leukoc Biol, 2000,
68:881-9).
[0135] In addition, the following experiment was performed to show
that HUVECs can colonize and proliferate on cell binding peptide
SEQ ID NO: 4-modified collagen. In 96-well plates 7,000 HUVECs were
plated on peptide-modified soluble collagen or unmodified collagen
for 48 hours at 37.degree. C. Plates were removed and washed and
the remaining attached cells were detected using CELLTITER-GLO on a
luminometer. The graph in FIG. 23 shows that HUVECs colonize and
proliferate equally on unmodified and cell binding peptide-modified
collagen (FIG. 23).
[0136] The presentation of cell binding peptide-modified collagen
to endothelial cells in a plate format may be very different than
an acellular, collagen-rich artery. Therefore, cell binding
peptide-modified HELISTAT collagen sponges were used to better
model the proposed vascular graft application. The cell binding
peptide-modified HELISTAT collagen sponges were generated according
to Example 7. HUVEC retention was compared for cell binding
peptide-modified- and unmodified-collagen sponges. Briefly,
peptide-modified or unmodified collagen sponges were rehydrated in
serum free medium containing 50,000 CELLTRACKER GREEN labeled
HUVECs. The sponges were incubated at RT rotating in PBS containing
2% FBS. At 1, 2, and 20 h the samples were placed in a new tube
with fresh buffer. After the 20 h incubation, the sponges were
digested with 100 U collagenase for 16 h and the remaining cells
enumerated. After 20 hours with agitation, the cell binding
peptide-modified sponge retained 5-fold more cells than the
unmodified collagen sponge (FIG. 24).
[0137] The ability of the collagen modified with endothelial cell
binding peptide SEQ ID NO: 4 to capture ECFCs in flow was analyzed
as follows. Glass coverslips were coated with unmodified collagen
or cell binding peptide modified-collagen and mounted in a
polycarbonate parallel plate flow chamber. PBS/10% FBS was
circulated through a closed 150 ml system to block the coverslips.
Approximately 2.times.10.sup.6 ECFC were injected into the system
and were circulated for 2 h at 37.degree. C. Coverslips were washed
in PBS to remove loosely adhering cells, the remaining cells on the
coverslips were lysed in CELLTITERGLO (INVITROGEN, CA), and the
cells enumerated by luminescence against a standard curve. The data
in FIG. 25A show that the peptide modified collagen captured about
20-fold more cells than the unmodified collagen.
[0138] The ability of the collagen modified with endothelial cell
binding peptide SEQ ID NO: 4 to retain HUVECs under shear stress
was analyzed as follows. Glass cover-slips were coated with peptide
conjugated collagen or unmodified collagen and seeded with HUVECs.
Coverslips were secured in a polycarbonate slide with six 1 cm
diameter wells enabling simultaneous testing of materials. A closed
loop peristaltic pump was used to expose the samples to flow
conditions for 30 minutes at laminar flow rates up to 12
dynes/cm.sup.2 in PBS containing 2% FBS. The number of cells
retained on the cover slip was determined using CELLTITER-GLO
(INVITROGEN) and a luminometer. The data in FIG. 25B show that the
peptide modified-collagen captured about 3-fold more cells than the
unmodified collagen, and the application of shear stress did not
significantly affect cell capture by peptide modified- or
unmodified-collagen.
Example 12
Differentiation of MSCs Captured with Stem Cell Binding Peptide
into Adipocytes, Osteoblasts, or Chondrocytes
[0139] This experiment was performed to determine whether MSCs
captured with a stem cell binding peptide retained the ability to
differentiate into cells of mesenchymal origin.
[0140] Adipocyte differentiation. After capture of MSCs using cell
binding peptide SEQ ID NO: 4 with the MILTENYI magnetic system
according to Example 6, the ability of the captured cells to
differentiate into an adipocyte lineage was examined. The MSCs
present in the MILTENYI column eluants (see Example 6) were
cultured for 21 days in complete medium (DMEM, 10% FBS, 100
units/mL penicillin, 100 .mu.g/mL streptomycin, and 2 mM glutamine)
supplemented with 0.5 mM isobutyl methylxanthine, 1 .mu.M
dexamethasone, 10 .mu.M insulin, 200 .mu.M indomethacin, and 1%
antibiotic/antimycotic. Following the 21 day incubation, the cells
were fixed in 4% paraformaldehyde in PBS for 15 minutes, washed in
60% isopropanol for 5 minutes, and stained with Oil Red 0 (SIGMA)
for 10 minutes to determine the extent of adipogenesis (see FIG.
26, panels A (undifferentiated MSCs) and panel B (adipocyte
differentiated MSCs)). The image of the adipose differentiated
cells (FIG. 26, panel B) contains a larger magnification inset
where the lipid vacuoles are clearly visible. The results shown in
panels A and B of FIG. 26 show that the adipogenesis pathway
remains intact for the MSCs after capture from bone marrow using
stem cell binding peptide SEQ ID NO: 4.
[0141] Osteoblast differentiation. For osteogenic differentiation,
the MSCs present in the MILTENYI column eluants (see Example 6)
were cultured for 14 days in complete medium supplemented with 0.1
.mu.M dexamethasone, 50 .mu.M ascorbate-2-phosphate, 10 mM
.beta.-glycerophosphate, and 1% antibiotic/antimycotic. Calcium
mineralization was measured by Alizarin Red S (SIGMA) staining to
reveal mineralizing osteoblasts (see FIG. 26, panel C
(undifferentiated MSCs) and panel D (osteoblast differentiated
MSCs)). The results shown in panels C and D of FIG. 26 show that
the osteogenic pathway remains intact for the MSCs after capture
from bone marrow using stem cell binding peptide SEQ ID NO: 4.
[0142] Chondrocyte differentiation. To examine chondrocyte
differentiation, the MSCs present in the MILTENYI column eluants
(see Example 6) were pelleted by centrifugation at 150.times.g for
5 minutes. Cells were washed once with 1 ml MACS NH CHONDRODIFF
Medium without disturbing the pellet. Cells were spun again and 1
mL CHONDRODIFF Medium was added to each pellet. Every third day,
medium was aspirated and replaced with fresh pre-warmed medium.
After 24 days in culture, cells exposed to CHONDRODIFF medium
formed cartilage plugs or nodules, whereas control cells formed
only loose or small nodules. Cells were washed once with PBS and
fixed in neutral buffered formalin overnight. Sections were
embedded in paraffin and sectioned at 5 microns. Sections were
examined by hemotoxylin and eosin staining (data not shown).
Sections were further examined by immunostaining for aggrecan, a
major structural component of cartilage. In FIG. 27, sections from
the periphery (panels A and B) or center (panels C and D) were
incubated with an antibody against aggrecan (ABCAM) (panels B and
D) or with secondary detection reagents only as a control (panels A
and C), then counterstained with DAPI to reveal cell nuclei. After
24 days in the culture medium, aggrecan could be detected in the
nodules formed from the MSCs captured by cell binding peptide SEQ
ID NO: 4. Control images of captured cells grown in the absence of
differentiation medium could not be taken due to the small and
loose nature of nodules.
Example 13
Enhanced Fibroblast Binding to Cell Binding Peptide-Modified
Collagen
[0143] This example demonstrates that collagen modified with
cell-binding peptide (SEQ ID NO: 4) binds more fibroblasts than
unmodified collagen. The experiment was performed according to the
following procedure. Cell-binding peptide (SEQ ID NO: 4) was
covalently attached to soluble collagen as described herein at
Example 7. 96-well plates were coated with various amounts of
unmodified or the peptide-modified collagen (177 .mu.mol peptide/g
collagen) over night at 4.degree. C. Unbound collagen was removed
and the plates were blocked for 1 h. After washing, 5,000 human
dermal fibroblasts were added per well in serum-free medium for 30
min at 37.degree. C. The plates were washed, and bound cells were
detected with CELLTITER-GLO (PROMEGA) using a luminometer. At
0.0025 .mu.g collagen, fibroblast binding was increased 11-fold for
the peptide-modified collagen compared to unmodified collagen (see
FIG. 28). Increased cell binding was also observed at higher
concentrations of the SEQ ID NO: 4 peptide-modified collagen (data
not shown).
Example 14
Identification of PDGF Binding Peptides by Phage Display
[0144] Peptides that bind PDGF were identified by phage display
biopanning. Enrichment of PDGF-binding phage in the selection was
monitored using an ELISA-type assay with an HRP-conjugated anti-M13
antibody. After enrichment for PDGF-BB specific phage, individual
phage were picked, propagated on E. coli, and tested for binding to
PDGF-BB. The DNA from phage displaying peptides that displayed
binding to rhPDGF-BB was analyzed, and the amino acid sequences of
the displayed peptides were deduced from the DNA sequence (see
Table 2; SEQ ID NOs: 21-27).
TABLE-US-00006 TABLE 2 Amino Acid Sequences from PDGF Phage Display
SEQ ID NO: Amino acid sequence (single letter code) 21
SSGSDPSSSWFPPPVWFSSR 22 SSLAAWYSSWGVS 23 SEATQASRNWEGIRVFLASR 24
SEWDQYYSYYLEH 25 SPWVTWYYSASSP 26 STMLSWDHVNLYYTMH 27
SPLLHWNKIQDYYRLN
[0145] The PDGF-binding peptide sequences were then synthesized
using standard solid-phase peptide synthesis techniques on a
SYMPHONY Peptide Synthesizer (PROTEIN TECHNOLOGIES, Tucson, Ariz.)
using standard Fmoc chemistry (HBTU/HOBT activation, 20% piperidine
in DMF for Fmoc removal). N-.alpha.-Fmoc-amino acids (with
orthogonal side chain protecting groups) were purchased from
Novabiochem. After all residues were coupled, simultaneous cleavage
and side chain deprotection was achieved by treatment with a
trifluoroacetic acid (TFA) cocktail. Crude peptide was precipitated
with cold diethyl ether and purified by high-performance liquid
chromatography on a WATERS ANALYTICAL/Semi-preparative HPLC unit on
VYDAC C18 silica column (preparative 10 .mu.m, 250 mm.times.22 mm)
using a linear gradient of water/acetonitrile containing 0.1% TFA.
Homogeneity of the synthetic peptides was evaluated by analytical
RP-HPLC (VYDAC C18 silica column, 10 .mu.m, 250 mm.times.4.6 mm)
and the identity of the peptides confirmed with MALDI-TOF-MS.
Biotinylated peptides were generated similarly, with a
GSSGK(biotin) sequence added to the C-terminus of the peptide.
[0146] The PDGF-BB binding peptides with the biotin moiety on their
C-terminus were tested for their ability to bind the target growth
factor using the following methods. Streptavidin-coated plates were
first prepared by generating a 1:100 dilution of streptavidin (1
mg/mL) in 0.1M NaHCO.sub.3 buffer. In each well of a 96-well
IMMULON 4HBX plate, 50 .mu.L of this solution was added (0.5 .mu.g
of streptavidin per well). Plates were incubated overnight at
4.degree. C. Wells were blocked with 150 .mu.L/well of bovine serum
albumin (1%) in 0.1M NaHCO.sub.3 buffer. Plates were either stored
at 4.degree. C. or incubated 1 hr at room temperature, if plates
were to be used immediately. Prior to use plates were washed three
times in TBS-T (TBS+0.05% Tween-20). Peptides were diluted to 0.2
.mu.M in 100 .mu.L of TBS-T. Peptide solution was added to each
well and incubated for 45 min at room temperature. Remaining
streptavidin binding sites were blocked with free biotin (0.5 mM).
Plates were washed three times in TBS-T to remove unbound peptide.
Growth factor solution (PDGF-BB), starting at 1 .mu.M was run
through a 2-fold dilution series to generate a range of
concentrations (1 .mu.M-1 nM) in a 50 .mu.L volume in each well.
Growth factor was added to each well and incubated for 40 min at
room temperature. Plates were washed five times in TBS-T to remove
unbound growth factor. Antibodies against growth factor PDGF-BB
were added (ABCAM Cat#:ab15499) for 30 min at room temperature.
Plates were washed with TBS-T and an alkaline
phosphatase-conjugated secondary antibody (anti-mouse, 1:1000
dilution) was added to each well. To reveal immunoreactivity, 100
.mu.L of para-nitrophenyl phosphate solution was added to each
well, and optical density was recorded on a spectrophotometer. The
results are shown in FIG. 29 (the numbers in FIG. 29 refer to SEQ
ID NOs: 21-27). The peptide having SEQ ID NO: 25 was observed to
have the best binding affinity for PDGF-BB. "Control` in FIG. 29 is
a negative control peptide known not to bind PDGF. The following
PDGF-binding sequence motif was generated based on the FIG. 29
results and allowing for conservative amino acid substitutions in
SEQ ID NO: 25:
small-small-Z-aliphatic-small-Z-Z-Z-small-aliphatic-small-small-small,
wherein "small" is S, T, G, or P; wherein "Z" is Y, W, or F; and
wherein "aliphatic" is A, V, I, or L (SEQ ID NO: 28).
[0147] In addition to the PDGF-binding sequences identified through
the phage display, additional PDGF-binding peptides were generated
by synthesizing the SEQ ID NO: 25 peptide with an acidic amino acid
sequence of varying lengths incorporated at the N-terminus (see
Table 3). The peptides in Table 3 were synthesized as described
above, and similarly tested for their ability to bind PDGF-BB using
the methods described above. Unexpectedly, enhanced binding
affinity for PDGF-BB was observed for the peptides with the
incorporated N-terminal acidic amino acid sequence (see FIG. 30;
the numbers in FIG. 30 refer to SEQ ID NOs: 25 and 29-32). The
following PDGF-binding sequence motifs were generated based on the
FIG. 30 results for the tagged peptides shown in Table 3: motif #1
is Tag-(SEQ ID NO: 28), wherein "Tag" is from 0-6 amino acids.
Another PDGF-binding sequence motif is as follows: motif #2 is
(D/E).sub.n1-(SEQ ID NO: 28)-(D/E).sub.n2, wherein D/E is aspartate
or glutamate, n1 and n2 are 0-6, and at least one of n1 or n2 must
be 0. Another PDGF-binding sequence motif is as follows: motif #3
is (D/E).sub.n1-(SEQ ID NO: 28), wherein D/E is aspartate or
glutamate, n1 is 0-6. Another PDGF-binding sequence motif based on
SEQ ID NO: 25 and the results in FIG. 30 is as follows: motif #4
((D/E).sub.n1-(SEQ ID NO: 25) wherein n1 is 0-6.
TABLE-US-00007 TABLE 3 PDGF Binding Peptides SEQ ID NO: Amino acid
sequence (single letter code) 29 DD-SPWVTWYYSASSP 30
DDDD-SPWVTWYYSASSP 31 DEDE-SPWVTWYYSASSP 32
DEDEDE-SPWVTWYYSASSP
[0148] The binding activity of the PDGF-binding peptide SEQ ID NO:
25 was further investigated by truncation analysis. Potentially the
most straightforward way to limit the complexity of peptide
synthesis is to reduce the number of amino acids included in the
length of the peptide sequence. The peptide SEQ ID NO: 25 was
shortened on both C and N termini to determine the minimal sequence
required for PDGF binding (see Table 4). Each truncated peptide was
synthesized with a biotin tag and, after purification, the
truncated peptides were immobilized on streptavidin plates for
PDGF-BB binding experiments as described above. FIG. 31 provides a
schematic diagram of the truncations generated and their
comparative PDGF binding capabilities compared to the SEQ ID NO: 25
peptide (the numbers in FIG. 31 refer to peptide SEQ ID NOs: 25 and
33-37). Slight decrements in binding relative to SEQ ID NO: 25 were
observed in SEQ ID NO: 33 (4 residues shorter than SEQ ID NO: 25)
and SEQ ID NO: 36 (2 residues shorter than SEQ ID NO: 25). The data
suggest a minimum PDGF binding domain in which 4 amino acids are
removed from the C terminus of SEQ ID NO: 25, i.e., SEQ ID NO: 33.
The following PDGF-binding sequence motifs were generated based on
the FIGS. 30 and 31 results for the tagged and truncated peptides
shown in Tables 3 and 4:
Tag.sub.1-small-small-Z-aliphatic-small-Z-Z-Z-small-Tag.sub.2 (SEQ
ID NO: 38), wherein "Tag.sub.1 and Tag.sub.2" are (D/E).sub.0-6,
wherein "small" is S, T, G, or P; wherein Z is Y, W, or F; wherein
"aliphatic" is A, V, I, or L; and wherein at least one of Tag.sub.1
or Tag.sub.2 must be 0. Another PDGF-binding sequence motif based
on SEQ ID NO: 33 and the FIGS. 30 and 31 results for the tagged and
truncated peptides is as follows:
Tag.sub.1-small-small-Z-aliphatic-small-Z-Z-Z-small (SEQ ID NO:
39), wherein "Tag.sub.1" is (D/E).sub.0-6, wherein "small" is S, T,
G, or P; wherein Z is Y, W, or F; wherein "aliphatic" is A, V, I,
or L. Another PDGF-binding sequence motif based on SEQ ID NO: 33
and the FIGS. 30 and 31 results for the tagged and truncated
peptides is as follows: motif #5 (D/E).sub.n1(SEQ ID NO: 33),
wherein n1 is 0-6.
TABLE-US-00008 TABLE 4 PDGF Binding Peptide Truncation Analysis SEQ
ID NO: Amino acid sequence (single letter code) 33 SPWVTWYYS 34
WVTWYYSASSP 35 TWYYSASSP 36 SPWVTWYYSAS 37 SPWVTWY
Example 15
Covalent Attachment of PDGF Binding Peptide to a Collagen
Substrate
[0149] In this experiment PDGF binding peptide (SEQ ID NO: 29) was
covalently attached to a collagen sponge (HELISTAT sponge; INTEGRA
LIFE SCIENCES). The PDGF binding peptide SEQ ID NO: 29 further
comprising an amino acid spacer and a cysteine functional group was
covalently bound to the collagen sponge using standard thioether or
disulfide chemistries. The ability of the PDGF binding
peptide-modified sponge to bind PDGF-BB was tested. PDGF binding
peptide-modified and unmodified sponges were incubated with PDGF-BB
at various concentrations for 30 min. After washing, the sponges
were incubated with an antibody to PDGF-BB (ABCAM), followed by an
alkaline phosphatase-linked secondary antibody (PROMEGA). Antibody
that bound to PDGF-BB on the sponge was detected with the
chromogenic substrate pNPP. The data in FIG. 32 show that PDGF
binding peptide-modified sponge bound more PDGF-BB than unmodified
sponge.
[0150] Next, the ability of the PDGF binding peptide-modified
sponge to deliver bioactive PDGF was assessed. PDGF binding
peptide-modified and unmodified collagen sponges were incubated
with PDGF-BB and then washed. The remaining bound PDGF-BB was
released by collagenase digestion, and the collagenase eluate was
added at a range of dilutions to HEK293 cells transfected with PDGF
receptor .beta.. After washing, the cells were incubated with an
antibody against phosphorylated PDGF receptor .beta. (pY857).
Tyrosine phosphorylation was assessed by flow cytometry. The eluate
from the unmodified sponges did not stimulate phosphorylation of
PDGF receptor .beta., whereas the eluate from the PDGF binding
peptide-modified sponges stimulated phosphorylation of the receptor
(FIG. 33A). When the remaining bound PDGF-BB was released by acid
elution instead of collagenase digestion, the eluates showed a
similar ability to stimulate tyrosine phosphorylation (data not
shown). In addition, the biological activity of acid-eluted PDGF-BB
was further assessed by measuring the ability of the eluted PDGF-BB
to induce cell proliferation by measuring BrdU incorporation into
NIH-3T3 cells. The eluates (n=3) were incubated with NIH-3T3 cells,
and cell proliferation was measured by ELISA as incorporation of
BrdU (ROCHE CELL PROLIFERATION ASSAY). The data in FIG. 33B show
that the eluate from PDGF binding peptide-modified sponge
stimulated cell proliferation significantly more than the eluate
from unmodified sponge. Taken together, these data indicate that
our PDGF binding peptide can bind and retain a bioactive form of
PDGF.
Example 16
Covalent Attachment of a Binding Peptide to Polyanhydride
Polymer
[0151] A binding peptide is covalently attached to polymaleic
anhydride (PMA) using established methods (Pompe, et al., 2003,
Biomacromolecules, 4(4):1072-9). First, a spacer, such as for
example, GSSGK, is added to a terminus of the peptide and the
peptide is attached to the PMA anhydride groups through the
reactive terminal lysine amine group on the peptide-spacer. A
schematic diagram of one example of this chemistry is shown in FIG.
6. PMA .about.5,000 MW is dissolved in anhydrous dimethylformamide
(DMF) and peptide is dissolved in DMF with excess
diisopropylethylamine (DIEA). The peptide solution is heated with
the PMA solution at 40.degree. C. overnight, for example, and the
reaction mixture quenched with water. The crude PMA-peptide
conjugate is filtered and analyzed. For example, the extent of
substitution on the polyanhydride polymer can be estimated by
integration of .sup.1H-NMR peaks from the peptide together with the
integrals of key reference peaks on the polymer to provide an
estimate of the level of peptide substitution. In another example,
size exclusion chromatography is used by monitoring the UV
absorption of the peptide along with a known amount of unconjugated
PMA. The degree of peptide substitution is estimated from the mass
of the lyophilized product and the UV absorbance of the peptide
component.
Example 17
GDF-7 Binding Peptides
[0152] GDF binding peptides disclosed in US Patent Application
Publication No. US 2009/0098175 A1 are provided, and, in
particular, the following GDF binding peptides from US Patent
Application Publication No. US 2009/0098175 A1 shown herein at
Table 5 (SEQ ID NOs: 40-43).
TABLE-US-00009 TABLE 5 GDF-7 Binding Peptides SEQ ID NO: Amino acid
sequence 40 ssGPREIWDSLVGVVNPGWsr 41 ssGGVGGWALFETLRGKEVsr 42
ssVAEWALRSWEGMRVGEAsr 43 W-X-X-F-E-(S/T)-L-X-G-X-E-X
Example 18
Covalent Attachment of Cell Binding Peptide to Dextran
[0153] Cell binding peptide SEQ ID NO: 4 having a C-terminal spacer
and lysine residue was covalently attached to dextran
(POLYSCIENCES, Inc, PA). Dextran (3-7M; 27.7 mg) was first oxidized
by dissolving the dextran in 6 mL of PBS buffer pH 7.5, adding
NaIO.sub.4 (90 mg), and the vortexing in the dark for 4 hours at
room temperature. The reaction mixture was dialyzed against
distilled water and lyophilized to give aldehyde activated dextran
as a white spongy mass. The peptide was reacted with the aldehyde
activated dextran in 0.1 M sodium acetate buffer at pH 5.5 for 3
hours in the dark. Approximately 10 mg of NaCNBH.sub.3 was added to
the reaction and incubated overnight at room temperature in the
dark. Unreacted peptide and other reagents were removed by
extensive dialysis against water.
[0154] To show that peptide SEQ ID NO: 4 conjugated to soluble
dextran described above retained cell binding activity, a stem cell
binding competition assay was performed with free peptide SEQ ID
NO: 4 by flow cytometry. The SEQ ID NO: 4 peptide-modified dextran
was mixed with human MSCs and then incubated with biotinylated stem
cell binding peptide SEQ ID NO: 4, the binding of which could be
measured by flow cytometry using neutravidin-phycoerythrin. The SEQ
ID NO: 4 peptide-modified dextran was a strong competitor of free
peptide SEQ ID NO: 4 with a 50% inhibition value below 1 .mu.M,
suggesting that the covalently attached stem cell peptide retains
its ability to bind MSCs and that the SEQ ID NO: 4 peptide-modified
dextran has a higher affinity for MSCs (data not shown).
[0155] The foregoing description of the specific embodiments of the
presently disclosed subject matter has been described in detail for
purposes of illustration. In view of the descriptions and
illustrations, others skilled in the art can, by applying current
knowledge, readily modify and/or adapt the presently disclosed
subject matter for various applications without departing from the
basic concept of the presently disclosed subject matter; and thus,
such modifications and/or adaptations are intended to be within the
meaning and scope of the appended claims.
Sequence CWU 1
1
43121PRTArtificial sequenceSynthetic 1Ser Ser Met Tyr Phe Ser Pro
Leu His Thr Trp Gln Ser Ala Pro Ser1 5 10 15Thr Ser Gly Ala Glu
20221PRTArtificial sequenceSynthetic 2Ser Ser Phe Arg Phe Gln Arg
Leu Glu Asp Trp Asn Tyr Pro Ser Asn1 5 10 15Thr Asp Asn Ala Glu
20321PRTArtificial sequenceSynthetic 3Ser Ser Gly Tyr Met Gln Phe
Gly His Leu Leu Asp Trp Thr Gly Ser1 5 10 15Pro Ser Gly Ser Arg
20419PRTArtificial sequenceSynthetic 4Ser Ser Phe Trp Asp Val Cys
Gln Gly Asp Gly Thr Cys Tyr Gly Gly1 5 10 15Gly Ser
Arg515PRTArtificial sequenceSynthetic 5Val Ala Asn Pro Phe Thr Tyr
Leu Ser Ala Trp Ser Asn Pro Leu1 5 10 15616PRTArtificial
sequenceSynthetic 6Glu Thr Leu Ile Phe Ser Lys Leu Gly Gln Trp Gly
Asn Ser Leu Ser1 5 10 15715PRTArtificial sequenceSynthetic 7Gly Tyr
Met Gln Phe Gly His Leu Leu Asp Trp Thr Gly Ser Pro1 5 10
15815PRTArtificial sequenceSynthetic 8Ser Val Tyr Arg Phe Asp Ser
Leu Thr Thr Trp Ser Ser Asn Gln1 5 10 15915PRTArtificial
sequenceSynthetic 9Gly Ser Trp Ser Phe Gly Thr Leu Gly Pro Trp Ser
Ser Ser Gln1 5 10 151015PRTArtificial sequenceSynthetic 10Trp Leu
Gly Asn Phe Asn Ala Leu Thr Asp Trp Pro Thr Asp Ser1 5 10
151115PRTArtificial sequenceSynthetic 11Thr Ser Gly Phe Phe Gly Ser
Leu Asp Thr Trp Pro Pro Thr Leu1 5 10 151212PRTArtificial
sequenceSynthetic 12Asn Tyr Trp Asn Phe Gly Pro Leu Glu Asp Tyr
Ser1 5 101312PRTArtificial sequenceSynthetic 13Ser Val Leu His Phe
His Pro Met Lys Ser Tyr Asp1 5 101412PRTArtificial
sequenceSynthetic 14Asn Ser Ile Tyr Phe Ser Pro Leu Arg Asp Tyr
Gln1 5 101512PRTArtificial sequenceSynthetic 15Gly His Phe Glu Tyr
Gly Arg Leu Gln Ser Ile Leu1 5 101620PRTArtificial
sequenceSynthetic 16Ser Ser Phe Arg Phe Gly Pro Leu Gly Thr Trp Asn
Tyr Pro Ser Thr1 5 10 15Asp Asn Ala Glu 201714PRTArtificial
sequenceSynthetic 17Xaa Xaa Phe Xaa Xaa Leu Xaa Xaa Trp Xaa Xaa Xaa
Xaa Xaa1 5 101814PRTArtificial sequenceSynthetic 18Xaa Xaa Xaa Xaa
Xaa Xaa Xaa Xaa Xaa Xaa Xaa Xaa Xaa Xaa1 5 101916PRTArtificial
sequenceSynthetic 19Xaa Xaa Xaa Xaa Xaa Cys Xaa Xaa Xaa Gly Thr Cys
Xaa Gly Gly Gly1 5 10 152016PRTArtificial sequenceSynthetic 20Xaa
Xaa Trp Xaa Xaa Cys Xaa Xaa Xaa Gly Thr Cys Xaa Gly Gly Gly1 5 10
152120PRTArtificial sequenceSynthetic 21Ser Ser Gly Ser Asp Pro Ser
Ser Ser Trp Phe Pro Pro Pro Val Trp1 5 10 15Phe Ser Ser Arg
202213PRTArtificial sequenceSynthetic 22Ser Ser Leu Ala Ala Trp Tyr
Ser Ser Trp Gly Val Ser1 5 102320PRTArtificial sequenceSynthetic
23Ser Glu Ala Thr Gln Ala Ser Arg Asn Trp Glu Gly Ile Arg Val Phe1
5 10 15Leu Ala Ser Arg 202413PRTArtificial sequenceSynthetic 24Ser
Glu Trp Asp Gln Tyr Tyr Ser Tyr Tyr Leu Glu His1 5
102513PRTArtificial sequenceSynthetic 25Ser Pro Trp Val Thr Trp Tyr
Tyr Ser Ala Ser Ser Pro1 5 102616PRTArtificial sequenceSynthetic
26Ser Thr Met Leu Ser Trp Asp His Val Asn Leu Tyr Tyr Thr Met His1
5 10 152716PRTArtificial sequenceSynthetic 27Ser Pro Leu Leu His
Trp Asn Lys Ile Gln Asp Tyr Tyr Arg Leu Asn1 5 10
152813PRTArtificial sequenceSynthetic 28Xaa Xaa Xaa Xaa Xaa Xaa Xaa
Xaa Xaa Xaa Xaa Xaa Xaa1 5 102915PRTArtificial sequenceSynthetic
29Asp Asp Ser Pro Trp Val Thr Trp Tyr Tyr Ser Ala Ser Ser Pro1 5 10
153017PRTArtificial sequenceSynthetic 30Asp Asp Asp Asp Ser Pro Trp
Val Thr Trp Tyr Tyr Ser Ala Ser Ser1 5 10 15Pro3117PRTArtificial
sequenceSynthetic 31Asp Glu Asp Glu Ser Pro Trp Val Thr Trp Tyr Tyr
Ser Ala Ser Ser1 5 10 15Pro3219PRTArtificial sequenceSynthetic
32Asp Glu Asp Glu Asp Glu Ser Pro Trp Val Thr Trp Tyr Tyr Ser Ala1
5 10 15Ser Ser Pro339PRTArtificial sequenceSynthetic 33Ser Pro Trp
Val Thr Trp Tyr Tyr Ser1 53411PRTArtificial sequenceSynthetic 34Trp
Val Thr Trp Tyr Tyr Ser Ala Ser Ser Pro1 5 10359PRTArtificial
sequenceSynthetic 35Thr Trp Tyr Tyr Ser Ala Ser Ser Pro1
53611PRTArtificial sequenceSynthetic 36Ser Pro Trp Val Thr Trp Tyr
Tyr Ser Ala Ser1 5 10377PRTArtificial sequenceSynthetic 37Ser Pro
Trp Val Thr Trp Tyr1 5389PRTArtificial sequenceSynthetic 38Xaa Xaa
Xaa Xaa Xaa Xaa Xaa Xaa Xaa1 5399PRTArtificial sequenceSynthetic
39Xaa Xaa Xaa Xaa Xaa Xaa Xaa Xaa Xaa1 54021PRTArtificial
sequenceSynthetic 40Ser Ser Gly Pro Arg Glu Ile Trp Asp Ser Leu Val
Gly Val Val Asn1 5 10 15Pro Gly Trp Ser Arg 204121PRTArtificial
sequenceSynthetic 41Ser Ser Gly Gly Val Gly Gly Trp Ala Leu Phe Glu
Thr Leu Arg Gly1 5 10 15Lys Glu Val Ser Arg 204221PRTArtificial
sequenceSynthetic 42Ser Ser Val Ala Glu Trp Ala Leu Arg Ser Trp Glu
Gly Met Arg Val1 5 10 15Gly Glu Ala Ser Arg 204312PRTArtificial
sequenceSynthetic 43Trp Xaa Xaa Phe Glu Xaa Leu Xaa Gly Xaa Glu
Xaa1 5 10
* * * * *