Immunogenic compositions and methods of use
16 claims: 3 independent, 13 dependent
- 1An immunogenic composition, comprising a multilayer film comprising two or more layers of polyelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes, wherein a first layer polyelectrolye comprises a first antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to about 250 amino acid residues, wherein the first antigenic polypeptide is not a homopolymer, is at least 15 amino acids long, and has an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml;wherein a second layer comprises a second layer polyelectrolyte comprising a polycationic material or a polyanionic material having a molecular weight of greater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide.
- 14An immunogenic composition for eliciting an immune response in a vertebrate organism, wherein the immunogenic composition comprises, a multilayer film comprising two or more layers of polyelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes, wherein a first layer polyelectrolye comprises an antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to about 250 amino acid residues, wherein the antigenic polypeptide is not a homopolymer, is at least 15 amino acids long, and has an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml;wherein a second layer comprises a second layer polyelectrolyte comprising a polycationic material or a polyanionic material having a molecular weight of greater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide.
- 15A method of making an immunogenic composition, the method comprising:depositing a first layer polyelectrolyte on a surface of a substrate to form a first layer;wherein, a first layer polyelectrolye comprises a first antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to about 250 amino acid residues, wherein the first antigenic polypeptide is not a homopolymer, is at least 15 amino acids long, and has an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml;depositing a second layer polyelectrolyte on the first layer polyelectrolyte to form a second layer;wherein a second layer comprises a second layer polyelectrolyte comprising a polycationic material or a polyanionic material having a molecular weight of greater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide. Anmelde-Nr: Application No: 06 844 221.9 Demande n°: Blatt Sheet Feullle Datum Date 04.01.2010 Date The examination is being carried out on the following application documents Description, Pages 1-36 as published Sequence listings part of the description, Pages 1-5 as published Claims, Numbers I- 10 filed with entry into the regional phase before the EPO II- 15 filed with telefax on 05-06-2009 Drawings, Sheets 1/4-4/4 as published Amendments The amendments filed with the telefax on 05.06.2009 are in not accordance with Article 123(2) EPC. No clear basis in the original application can be found for the the non-therapeutic method of claim 15, since the passage in paragraph [00102] relates to a therapeutic use only. Patentability Amended claim 15 is directed to a method of eliciting a non-therapeutic immune response in a vertebrate organism. The step of administering encompasses a surgical method (e.g. intravenous or intramuscular administation, see paragraph [00102]), which may not be patentable under Article 53(c) EPC (see also pending decision G1/07). Furthermore, the present method encompasses the use of human beings to raise antibodies, which is contrary to morality, and therefore not acceptable under Article 53(a) EPC. Novelty The present application does not meet the criteria of Article 54 EPC, because the subject - matter of claim 1 is not new. The document D1 discloses (the references in parentheses applying to this document) a multilayer film wherein a first layer comprises polypeptides which have 32 or 48 amino acid residues and which comprise one or more amino acid sequence motifs EPO Form 2906 01.91TRI Anmelde-Nr: Application No: 06 844 221.9 Demanden“: Blatt Sheet Feullle Datum Date 04.01.2010 Date consisting of from 5 to 15, preferably 7, amino acid residues and having a magnitude of a net charge per residue of more than 0.5 at neutral pH (see abstract, figures 1-3, 6 and page pages 294-297). Due to their net charge greater than 0.5, the first peptide of D1 has inherently an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml. The second layer comprises oppositely-charged polyelectrolytes (see page 294). Since the immunogenic composition is defined only in terms of the multilayer film and all the technical features of the claimed multilayer film are disclosed in D1, the subjectmatter of independent claim 1 is not new. The document D2 discloses (the references in parentheses applying to this document) a multilayer film wherein a first layer comprises polypeptides which comprise one or more amino acid sequence motifs consisting of from 5 to 15, preferably 7, amino acid residues and having a magnitude of a net charge per residue of more than 0.5 at neutral pH (see paragraphs [0061 -0065], claim 21, figures 1 and 5). Due to their net charge greater than 0.5, the first peptide of D2 has inherently an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml. The second layer comprises oppositely-charged polyelectrolytes. Since the immunogenic composition is defined only in terms of the multilayer film and all the technical features of the claimed multilayer film are disclosed in D2, the subjectmatter of independent claim 1 is not new. The applicant argues in his letter of 05.06.2009 that the polypeptides of the films of D1 and D2 do not have an antigenic determinant region covalently linked to the known surface absorption region. However, the antigenic determinant region of claim 1 is only defined by the number of amino acid residues of at least three amino acid residues. An antigenic determinant region of three amino acid residues covalently linked to a short surface adsorption region of e.g. five amino acids falls under the scope of the polypeptides of the films of D1 and D2. It is also noted that such polypeptides are capable of eliciting an immune response, see also paragraphs [0035] and [0036] of the present application. Consequently, there seems to be no structural or even a functional difference between an antigenic determinant region on the one hand and a surface adsorption region on the other hand. Clarity Claim 1 is unclear in the sense of Article 84 EPC, because the antigenic polypeptide comprises surface adsorption region(s) and antigenic determinant region(s), wherein the antigenic polypeptide and the surface adsorption region(s) have the same polarity. It is unclear how the antigenic polypeptide and one of its component can have the same polarity. It seems that the phrase should read as wherein the one or more antigenic determinant regions and the one or more surface adsorption regions have the same (net) polarity. Conclusion EPO Form 2906 01.91TRI Anmelde-Nr: Application No: 06 844 221.9 Demande n°: Blatt Sheet Feullle Datum Date 04.01.2010 Date It is not at present apparent which part of the application could serve as a basis for a new, allowable claim. Should the applicant nevertheless regard some particular matter as patentable, an independent claim should be filed taking account of Rule 43(1) EPC. The applicant should also indicate how the subject-matter of the new claim differs from the state of the art and the significance thereof. EPO Form 2906 01.91TRI 05/06 '09 16:35 FAX 441865305111 EPO MUNICH @004 11. The immunogenic composition of claim 1, wherein the multilayer film encapsulates one or more non-peptide bioactive molecule. 12. The immunogenic composition of claim 1, wherein the multilayer film is in the form of a microcapsule. 13. The immunogenic composition of claim 12, wherein the microcapsule comprises a core, and the core comprises an additional bioactive molecule wherein the additional bioactive molecule comprises a drug, a protein, an oligonucleotide, a nucleic acid, a lipid, a phospholipid, a carbohydrate, a polysaccharide, a lipopolysaccharide, or a combination of one or more of the foregoing bioactive molecules. 14. An immunogenic composition for eliciting a therapeutic immune response in a vertebrate organism, wherein the immunogenic composition comprises, a multilayer film comprising two or more layers of polyelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes, wherein a first layer polyelectrolye comprises an antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to about 250 amino acid residues, wherein the antigenic polypeptide is not a homopolymer, is at least 15 amino acids long, and has an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml;wherein a second layer comprises a second layer polyelectrolyte comprising a polycationic material or a polyanionic material having a molecular weight of greater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide. Received at the EPO on Jun 05, 2009 17:31:09. Page 4 of 8 05/06 '09 16:35 FAX 441865305111 -> EPO MUNICH @005 15. A method of eliciting a non-therapeutic immune response in a vertebrate organism, comprising administering into the vertebrate organism an immunogenic composition comprising a multilayer film comprising two or more layers of polyelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes, wherein a first layer polyelectrolye comprises an antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to about 250 amino acid residues, wherein the antigenic polypeptide is not a homopolymer, is at least 15 amino acids long, and has an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml;wherein a second layer comprises a second layer polyelectrolyte comprising a polycationic material or a polyanionic material having a molecular weight of greater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide.
- 16A method of making an immunogenic composition, the method comprising:depositing a first layer polyelectrolyte on a surface of a substrate to form a first layer;wherein, a first layer polyelectrolye comprises a first antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions, comprises one or more amino acid sequence motifs, the one or more amino acid sequence Received at the EPO on Jun 05, 2009 17:31:09. Page 5 of 8 05/06 16:36 09 י FAX 441865305111 -» EPO MUNICH @006 motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to about 250 amino acid residues, wherein the first antigenic polypeptide is not a homopolymer, is at least 15 amino acids long, and has an aqueous solubility at pH 4 to 10 of greater than 50 μg/ml;depositing a second layer polyelectrolyte on the first layer polyelectrolyte to form a second layer;wherein a second layer comprises a second layer polyelectrolyte comprising a polycationic material or a polyanionic material having a molecular weight of greater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide.
Independent claims4
2,421 paragraphs in 218 sections, as filed
The present application does not meet the criteria of Article 33(1) PCT, because the subject-matter of claim 1 is not new in the sense of Article 33(2) PCT.
The document D1 discloses (the references in parentheses applying to this document) a multilayer film wherein a first layer comprises polypeptides which have 32 or 48 amino acid residues and which comprise one or more amino acid sequence motifs consisting of from 5 to 15, preferably 7, amino acid residues and having a magnitude of a net charge per residue of more than 0.5 at neutral pH (see abstract, figures 1-3, 6 and page pages 294297). Due to their net charge greater than 0.5, the first peptide of D1 has inherently an aqueous solubility at pH 4 to 10 of greater than 50 /2g/ml. The second layer comprises oppositely-charged polyelectrolytes (see page 294).
Since the immunogenic composition is defined only in terms of the multilayer film and all the technical features of the claimed multilayer film are disclosed in D1, the subject-matter of independent claim 1 is not new.
The document D2 discloses (the references in parentheses applying to this document) a multilayer film wherein a first layer comprises polypeptides which comprise one or more amino acid sequence motifs consisting of from 5 to 15, preferably 7, amino acid residues and having a magnitude of a net charge per residue of more than 0.5 at neutral pH (see paragraphs [00610065־], claim 21, figures 1 and 5). Due to their net charge greater than 0.5, the first peptide of D2 has inherently an aqueous solubility at pH 4 to 10 of greater than 50 Mg/ml. The second layer comprises oppositely-charged polyelectrolytes.
Since the immunogenic composition is defined only in terms of the multilayer film and all the technical features of the claimed multilayer film are disclosed in D2, the subject-matter of independent claim 1 is not new.
Form PCT/ISA/237 (Separate Sheet) (Sheet 2) (EPO-April 2005)
International application No.
WRITTEN OPINION OF THE
INTERNATIONAL SEARCHING
AUTHORITY (SEPARATE SHEET)
The same reasoning applies, mutatis mutandis, to the subject-matter of the corresponding independent claims 18 and 20, which therefore is also considered not new.
Dependent claims 2-17 and 19 do not contain any features which, in combination with the features of any claim to which they refer, meet the requirements of the PCT in respect of novelty and/or inventive step, see documents D1 to D9 and the corresponding passages cited in the search report.
Industrial applicability
The polypeptide films can be used in the industrial production of pharmaceuticals. Therefore, the subject-matter of claims 1 to 17 and 20 meets the requirements of Article 33(4) PCT.
For the assessment of the present claims 18 and 19 on the question whether they are industrially applicable, no unified criteria exist in the PCT Contracting States. The patentability can also be dependent upon the formulation of the claims. The EPO, for example, does not recognize as industrially applicable the subject-matter of claims to the use of a compound in medical treatment, but may allow, however, claims to a known compound for first use in medical treatment and the use of such a compound for the manufacture of a medicament for a new medical treatment.
Re Item VI
Certain documents cited
Certain published documents
HAYNIE DT ET AL: Protein-inspired multilayer nanofilms: science, technology and medicine NANOMEDICINE: NANOTECHNOLOGY, BIOLOGY AND MEDICINE, vol. 2,
Form PCT/ISA/237 (Separate Sheet) (Sheet 3) (EPO-April 2005)
WRITTEN OPINION OF THE
INTERNATIONAL SEARCHING
AUTHORITY (SEPARATE SHEET)
International application No.
no. 3, September 2006 (2006-09), pages 150-157, XP002438718 ISSN: 15499634־
Form PCT/ISA/237 (Separate Sheet) (Sheet 4) (EPO-April 2005)
Anmelde-Nr.:
Application No.:
Demande n°:
Blatt
Sheet
Feuille
Date 2 6.01.2009
Date
844 221.9
The examination is being carried out on the following application documents:
Description, Pages
1-36 as published
Sequence listings part of the description, Pages
1-5 as published
Claims, Numbers
-15 filed with entry into the regional phase before the EPO
Drawings, Sheets
1/4-4/4 as published
Reference is made to the following documents; the numbering will be adhered to in the rest of the procedure:
D1: ZHENG B ET AL: Design of peptides for thin films, coatings and microcapsules for applications in biotechnology JOURNAL OF BIOMATERIALS SCIENCE POLYMER EDITION 05, vol. 16, no. 3, March 2005 (2005-03), pages 285-299, XP008078451 ISSN: 0920-5063
D2: US 2005/069950 A1 (HAYNIE DONALD T [US]) 31 March 2005 (2005-03-31)
D3: US-A-6 020 175 (ONDA MITSUHIKO [JP] ET AL) 1 February 2000 (2000-02-01)
D4: LI BINGYUN ET AL: Multilayer biomimetics: Reversible covalent stabilization of a nanostructured biofilm BIOMACROMOLECULES, AMERICAN CHEMICAL SOCIETY, US, vol. 5, no. 5, September 2004 (2004-09), pages 1667-1670, XP002414900 ISSN: 1525-7797
D5: WO 02/17888 A2 (MAX PLANCK GESELLSCHAFT [DE]; ANTIPOV ALEXEI [DE];
EPA Form 2906 12.07CSX
Anmelde-Nr.:
Application No.:
Demands n°:
Blatt
Sheet
Feuille
844 221.9
Date 26.01.2009
Date
VIEIRA EURIDICE [DE) 7 March 2002 (2002-03-07)
D6: HUA Al ET AL: BIOMEDICAL APPLICATIONS OF ELECTROSTATIC LAYER-BYLAYER NANO-ASSEMBLY OF POLYMERS, ENZYMES, AND NANOPARTICLES CELL BIOCHEMISTRY AND BIOPHYSICS, TOTOWA, NJ, US, vol. 39, no. 1, August 2003 (2003-08), pages 23-43, XP009070112 ISSN: 1085-9195
D7: WO 03/099835 A (UNIV EMORY [US]; CHAIKOF ELLIOT L [US]; SUN XUE-LONG [US]) 4 December 2003 (2003-12-04)
D8: US-A-5 138 026 (MIYASAKA TSUTOMU [JP] ET AL) 11 August 1992 (1992-08-11)
D9: GLINEL K ET AL.: Polyelectrolyte multilayers based on amphiphilic polysaccharides: Application for entrapment and release of hydrophobic molecules ABSTRACTS OF PAPERS AMERICAN CHEMICAL SOCIETY, vol. 230, 28 August 2005 (2005-08-28), page U3590, XP008078459 ISSN: 0065-7727
D10: HAYNIE DT ET AL: Protein-inspired multilayer nanofilms: science, technology and medicine NANOMEDICINE: NANOTECHNOLOGY, BIOLOGY AND MEDICINE, vol. 2, no. 3, September 2006 (2006-09), pages 150-157, XP002438718 ISSN: 1549-9634
Amendments
The amendments filed with entry into the regional phase before the EPO are in accordance with Article 123(2) EPC, since no supplementary subject-matter has been added.
Novelty
The present application does not meet the criteria of Article 54 EPC, because the subject-matter of claim 1 is not new.
The document D1 discloses (the references in parentheses applying to this document) a multilayer film wherein a first layer comprises polypeptides which have 32 or 48 amino acid residues and which comprise one or more amino acid sequence motifs consisting of from 5 to 15, preferably 7, amino acid residues and having a magnitude of a net charge per residue of more than 0.5 at neutral pH (see abstract, figures 1-3, 6 and page pages 294
ERA Form 2906 12.07CSX
Anmelde-Nr.:
Application No,:
Demande n°:
Blatt
Sheet 3
Feuille
Datum
Date 26.01.2009
Date
844 221.9
297). Due to their net charge greater than 0.5, the first peptide of D1 has inherently an aqueous solubility at pH 4 to 10 of greater than 50 ^g/ml. The second layer comprises oppositely-charged polyelectrolytes (see page 294).
Since the immunogenic composition is defined only in terms of the multilayer film and all the technical features of the claimed multilayer film are disclosed in D1, the subject-matter of independent claim 1 is not new.
The document D2 discloses (the references in parentheses applying to this document) a multilayer film wherein a first layer comprises polypeptides which comprise one or more amino acid sequence motifs consisting of from 5 to 15, preferably 7, amino acid residues and having a magnitude of a net charge per residue of more than 0.5 at neutral pH (see paragraphs [0061-0065], claim 21, figures 1 and 5). Due to their net charge greater than 0.5, the first peptide of D2 has inherently an aqueous solubility at pH 4 to 10 of greater than 50 /zg/ml. The second layer comprises oppositely-charged polyelectrolytes.
Since the immunogenic composition is defined only in terms of the multilayer film and all the technical features of the claimed multilayer film are disclosed in D2, the subject-matter of independent claim 1 is not new.
It is noted that claim 14 is not fully considered as a second medical use claim according to Article 54(5) EPC, because the claim is not clearly directed to the treatment of a disease in the sense of Article 53(c) EPC. The expression for eliciting an immune response in a vertebrate organism in claim 14 also refers to a method for producing antibodies in a vertebrate for a non-medical purpose. Therefore, the expression for eliciting an immune response in a vertebrate organism is not considered as a limiting technical feature in claim
14.
A clear indication of a disease is needed to render claim 14 novel over D1 and D2.
The document D10 might become relevant as document under Article 54(1)(2) EPC, if the priority date of the present application is not validly claimed. Since claim 1 is not considered to be new vis-^-vis the documents D1 and D2 anyway, an analysis of the priority document has not been performed yet. The applicant is, however, invited to indicate a basis for the present claims in the priority document.
EPA Form 2906 12.07CSX
Anmelde־Nr.:
Application No.:
Demands n<sup>e</sup>:
Blatt
Sheet 4
Feuille
Datum
Date 26.01.2009
Date
844 221.9
It is noted that dependent claims 2-13 and inter-related independent claim 15 do not contain any features which, in combination with the features of any claim to which they refer, meet the requirements of the EPC in respect of novelty and/or inventive step, see documents D1 to D9 and the corresponding passages cited in the search report.
Conclusion
The applicant is kindly requested to file a new set of claims which take into account the above mentioned comments.
When filing amended claims the applicant should at the same time bring the description into conformity with the amended claims. Care should be taken during revision, especially of the introductory portion and any statements of problem or advantage, not to add subject-matter which extends beyond the content of the application as originally filed (Article 123(2) EPC).
In order to facilitate the examination of the conformity of the amended application with the requirements of Article 123(2) EPC, the applicant is requested to clearly identify the amendments carried out, irrespective of whether they concern amendments by addition, replacement or deletion, and to indicate the passages of the application as filed on which these amendments are based.
If the applicant regards it as appropriate these indications could be submitted in handwritten form on a copy of the relevant parts of the application as filed.
EPA Form 2906 12.07CSX
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רשות הפטנטים
מדינת ישראל משרד המשפטים
פ.ק. 25
תאריך: י״ח אלול תשס״ט 07.09.2009 מספרכם: 136962
לכבוד
ריינהולד כהן ושותפיו
רחוב הברזל 26א׳
רמת החייל 69710
א.ג.נ.,
הנדון: מודעה על ליקויים בבקשת פטנט מס' 179660 סימוכין: מכתבכם מיום 15/07/2008
לתשומת לבכם: מקום בו הנכם מופנים לחוק, הכוונה היא לחוק הפטנטים, התשכ״ז - 1967. מקום בו הנכם מופנים לתקנות, הכוונה היא לתקנות הפטנטים (נוהלי הלשכה, סדרי דין, מסמכים ואגרות), התשכ״ח - 1968. בהתאם להוראות תקנה 41 הנני להודיעכם כי נמצאו בבקשה הנ״ל הליקויים המפורטים להלן.
עליכם להשיב על הודעה זו תוך ארבעה חודשים מתאריכה, אך הנכם רשאים לבקש את הארכת התקופה. עם בקשה כאמור שתוגש לפני תום התקופה יש לשלם אגרה בסך 59 ש״ח בעד כל חודש או חלק ממנו.
הבקשה נבחנה לאחר החלפת מערכת התביעות לגירסא 2 ואלו הליקוים:
1. לאור הסברכם שהוגש לרשות וצמצום האמצאה הנני מסיר את ההשגות עפ״י הוראות הסעיפים 4 ו 5 לחוק. בהתאם לתקנה 20(א)(1) עליכם להזכיר בפירוט את הפרסומים שצוטטו כלפי הבקשה בתור ידע קודם תוך צירוף דברי הסבר מתאימים.
2. קראתי היטב את הסברכם בנוגע לאחידות האמצאתית שבמערכת התביעות. במכתבכם שבסימוכין הנכם מציינים כי מערכת התביעות הנוכחית מתייחסת לפולינוקלאוטיד המקודד לתימדין קינאז כאשר יש לו מוטציה בעמדה 329 ו/או 330 באתר splice donor עם או בלי מוטציה באתר splice acceptor. היבט זה אינו בא לידי ביטוי במערכת התבועוחבתביעה 1 מציינת בפירוש בנוגע לפולינוקלאוטיד הנתבע כי לא קיים שינו/^ס^אתר splice acceptor (splice acceptor sites are not altered). לפיפך, תביעות ^/ז^המתייחסות לפולינוקלאוטידים
בהם קיים שינוי באתר splice acceptor חורגות מתחום האמצאה כפי שנתבע בתביעה 1. נא תגובתכם.
3. למרות האמור בסעיף 6 של מכתבכם שבסימוכין, המונח substantially עדיין קיים במערכת התביעות (ראו בתביעות 26 ו - 27).
4. שיוכה של תביעה 2 לתביעה 2 אינה ברורה ויש לשייך את התביעה כהלכה.
5. שיוכה של תביעה 3 לתביעה 3 אינה ברורה ויש לשייך את התביעה כהלכה.
בכבוד רב,
ערן רוס
בוחן פטנטים ראשי
רחוב אגודת ספורט הפועל מס׳ 1, הגן הטכנולוגי, בניין מס׳ 5, מיקוד 96951. טל׳: 5651666־2־972 פקס: 5651641־2־972 uzwwyt \,4 xAh^jt nj).
y/λρ 1Λ r£yOA
WIPO Reformed IPC: Internet Publication
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דף 1 מתוך 2
Family list application(s) for: W02007050702 (A2)
Sorting criteria: Priority Date Inventor Applicant Ecla
Immunogenic compositions and methods of use
Inventor: HAYNIE DONALD TEMPLETON Applicant: HAYNIE DONALD
EC: C07K17/00; Y01N6/00 IPC: A61K39/00; C07K17/00; A61K39/00; (+1)
Publication AU2006306202 (A1) - 2007-05-03 Priority Date: 2005-10-25 info:
- Multilayer films, coatings and microcapsules comprising <sup>z</sup> polypeptides
Inventor: HAYNIE DONALD TEMPLETON Applicant: LOUISIANA TECH UNIVERSITY
FOUN
EC: C07K17/00; Y01N6/00 IPC: C07K17/00; C07K17/00
Publication AU2006347951 (A1) - 2008-03-13 Priority Date: 2005-10-25 info:
IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
Inventor: HAYNIE DONALD TEMPLETON [US] Applicant: HAYNIE DONALD TEMPLETON [US]
EC: C07K17/00; Y01N6/00 IPC: A61K39/00; C07K17/00; A61K39/00; (+1)
Publication CA2627376 (A1) - 2007-05-03 Priority Date: 2005-10-25 info:
. MULTILAYER FILMS, COATINGS AND MICROCAPSULES <sup>4</sup> COMPRISING POLYPEPTIDES inventor: HAYNIE DONALD TEMPLETON [US] Applicant: LOUISIANA TECH UNIVERSITY RES
[US]
EC: C07K17/00; Y01N6/00 IPC: C07K17/00; C07K17/00
Publication CA2632703 (A1) - 2008-03-13 Priority Date: 2005-10-25 info:
Immunogenic compositions and methods of use
Inventor: Applicant: ARTIFICIAL CELLTECH [US]
EC: C07K17/00; Y01N6/00 IPC: A61K39/00; C07K17/00; A61K39/00; (+1)
Publication CN101296945 (A) - 2008-10-29 Priority Date: 2005-10-25 info:
Immunogenic compositions and methods of use
Inventor: Applicant: LOUISIANA TECH UNIVERSITY
FOUN [US]
EC: C07K17/00; Y01N6/00 IPC: C07K17/00; C07K17/00
Publication CN101365724 (A) - 2009-02-11 Priority Date: 2005-10-25 info:
)7 IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
Inventor: HAYNIE DONALD TEMPLETON [US] Applicant: HAYNIE DONALD TEMPLETON [US]
EC: C07K17/00; Y01N6/00 IPC: A61K39/00; C07K17/00; A61K39/00; (+1)
Publication EP1948695 (A2) - 2008-07-30 Priority Date: 2005-10-25 info:
_ MULTILAYER FILMS, COATINGS AND MICROCAPSULES ° COMPRISING POLYPEPTIDES
Inventor: HAYNIE DONALD TEMPLETON [US] Applicant: LOUISIANA TECH UNIVERSITY RES
[US]
EC: C07K17/00; Y01N6/00 IPC: C07K17/00; C07K17/00
Publication EP1948696 (A2) - 2008-07-30 Priority Date: 2005-10-25 info:
POLYPEPTIDE MULTILAYER FILMS AND METHODS
Inventor: Applicant:
EC: C07K17/00; Y01N6/00 IPC: A61K39/00; A61K39/02; A61K39/21; (+16)
Publication JP2009513651 (T) - 2009-04-02 Priority Date: 2005-10-25 info:
..oc?DB=EPODOC&locale=en EP&FT-D&CC-WO&NR=2007050702A2&KC=A2 16/09/2010 espacenet □ INPADOC Patent Family
דף 2 מתוך 2
POLYPEPTIDE MULTILAYER FILMS AND METHODS
Inventor: Applicant:
EC: C07K17/00; Y01N6/00 IPC: A61K47/42; B01J13/04; C07K14/00; (+3)
Publication JP2009513654 (T) - 2009-04-02 Priority Date: 2005-10-25 info:
IMMUNOGENIC COMPOSITIONS AND METHODS OF USE.
Inventor: HAYNIE DONALD TEMPLETON [US]
EC: C07K17/00; Y01N6/00
Publication MX2008005364 (A) - 2008-11 -20 info:
Method for controlling stability of nanofabricated polypeptide multilayer films, coatings, and microcapsules
Inventor: HAYNIE DONALD T [US]
Applicant: ARTIFICIAL CELL TECHNOLOGIES INC [US]
IPC: A61K39/00; C07K17/00; A61K39/00; (+1)
Priority Date: 2005-10-25
EC: G01N33/68A
Publication US2006147543 (A1) - 2006-07-06 info: US7321022 (B2) - 2008-01-22
Method for designing polypeptides for the nanofabrication of thin films, coatings, and microcapsules by electrostatic layer-by-layer self assembly Inventor: HAYNIE DONALD T [US]
Applicant: LOUISIANA TECH UNIVERSITY FOUNDATION, INC
IPC: A61K9/16; A61K9/50; G01N33/68; (+3)
Priority Date: 2003-08-29
EC: G01N33/68A
Publication US2005069950 (A1) - 2005-03-31 info: US7348399 (B2) - 2008-03-25
Artificial red blood cells
Applicant: HAYNIE DONALD T, ; LOUISIANA
TECH UNIVERSITY FOUNDATION, INC
IPC: G01N33/68; G01N33/68; (IPC17): G01N33/53
Priority Date: 2003-08-29
Inventor: HAYNIE DONALD T [US]
Applicant: LOUISIANA TECH UNIVERSITY FOUNDATION
IPC: A61K38/42; A61K9/16; A61K9/50; (+7)
Priority Date: 2003-08-29
EC: G01N33/68A
Publication US2006205005 (A1) - 2006-09-14 info: US7411038 (B2) - 2008-08-12
Nanofabricated Polypeptide Multilayer Films, Coatings, and
Microcapsules
Inventor: HAYNIE DONALD T [US]
EC: G01N33/68A
Publication US2008125575 (A1) - 2008-05-29 info: US7534860 (B2) - 2009-05-19
Applicant: LOUISIANA TECH UNIVERSITY FOUN [US]
IPC: C07K16/00; G01N33/68; C07K16/00; (+1)
Priority Date: 2003-0829־
Data supplied from the espacenet database — Worldwide
..oc?DB=EPODOC&locale=en EP&FT=D&CC=WQ&NR=2007050702A2&KC=A2 16/09/2010 espacenet □ INPADOC Patent Family
דף 1 מתוך 2
Family list application(s) for: W02007050702 (A2)
Sorting criteria: Priority Date Inventor Applicant Ecla <sub>1 R</sub> Method for Controlling Stability of Nanofabricated Polypeptide Multilayer Films, Coatings, and Microcapsules
Inventor: HAYNIE DONALD T [US] Applicant: LOUISIANA TECH UNIVERSITY
FOUN [US]
EC: G01N33/68A IPC: C07K14/00,: G01N33/68; C07K14/00; (+1)
Publication US2009054633 (A1) - 2009-02-26 Priority Date: 2003-08-29 info: US7538184 (B2) - 2009-05-26 <sub>7 י</sub> Multilayer films, coatings, and microcapsules comprising polypeptides
Inventor: HAYNIE DONALD T [US] Applicant: LOUISIANA TECH FOUNDATION, INC
EC: A61K39/00; A61K39/012; (+5) IPC: A61K9/16; A61K9/50; A61K9/16; (+1)
Publication US2007077276 (A1) - 2007-04-05 Priority Date: 2003-08-29 info: US7544770 (B2) 2009-06-09 ־ <sub>1 R</sub> Multilayer films, coatings, and microcapsules comprising polypeptides
Inventor: HAYNIE DONALD T [US] Applicant: LOUISIANA TECH UNIVERSITY
FOUNDATION, INC
EC: A61K39/00; A61K39/012; (+5) IPC: A61K9/16,: A61K9/50; A61K9/16; (+1)
Publication US2007077275 (A1) - 2007-04-05 Priority Date: 2003-08-29 info: US7550557 (B2) - 2009-06-23
Immunogenic compositions and methods of use
Inventor: HAYNIE DONALD T [US] Applicant: ARTIFICIAL CELL TECHNOLOGIES,
INC
EC: A61K39/00; A61K39/012; (+5) IPC: A61K39/38; A61K9/16; A61K9/50; (+3)
Publication US2007077253 (A1) - 2007-04-05 Priority Date: 2003-08-29 info: US7615530 (B2) - 2009-11-10
IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
Inventor: HAYNIE DONALD T [US] Applicant: ARTIFICIAL CELL TECHNOLOGIES I
[US]
EC: C07K17/00; Y01N6/00 IPC: A61K39/00; A61K9/50; A61K9/70; (+3)
Publication US2010028410 (A1) - 2010-02-04 Priority Date: 2005-10-25 info: US7781399 (B2) - 2010-08-24
IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
Inventor: HAYNIE DONALD T [US] Applicant: ARTIFICIAL CELL TECHNOLOGIES I
[US]
EC: C07K17/00; Y01N6/00 IPC: A61K38/17; A61K38/45; A61K9/50; (+7)
Publication US2010028424 (A1) - 2010-02-04 Priority Date: 2005-10-25 info: US7786076 (B2) - 2010-08-31 __ Method for design of polypeptides for nanofabrication of multilayer films, coatings, and microcapsules
Inventor: HAYNIE DONALD T [US] Applicant:
EC: G01N33/68A IPC: G01N33/68; G06F19/00; G01N33/68; (+1)
Publication US2006155482 (A1) - 2006-07-13 Priority Date: 2003-08-29 info:
Polypeptide multilayer films and methods
Inventor: HAYNIE DONALD T [US] Applicant:
EC: C07K17/00; Y01N6/00 IPC: C12M3/00; G01N33/53; C12M3/00; (+1)
Publication US2008020402 (A1) - 2008-01-24 Priority Date: 2005-10-25 info:
Multilayer Films, Coatings, and Microcapsules Comprising
Polypeptides
Inventor: HAYNIE DONALD T [US] Applicant: FOUNDATION [US]
..=l&KC=A2&NR=2007050702A2&DB=EPODOC&locale=en EP&CC=WO&FT=D 16/09/2010 espacenet 0 INPADOC Patent Family
דף 2 מתוך 2
EC: A61K39/00; A61K39/012; (+5) IPC: B05D5/12; B32B27/08; B32B27/32; (+7)
Publication US2009233074 (A1) - 2009-09-17 Priority Date: 2003-08-29 info:
IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
Inventor: HAYNIE DONALD T [US] Applicant: ARTIFICIAL CELL TECHNOLOGIES I
[US]
EC: C07K17/00; Y01N6/00 IPC: A61K39/002; A61K39/015; A61K9/50; (+2)
Publication US2010028423 (A1) - 2010-02-04 Priority Date: 2005-10-25 info:
IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
Inventor: HAYNIE DONALD T [US] Applicant: ARTIFICIAL CELL TECHNOLOGIES I
[US]
EC: C07K17/00; Y01N6/00 IPC: A61K39/02; A61K39/04; A61K39/05; (+17)
Publication US2010028448 (A1) - 2010-02-04 Priority Date: 2005-10-25 info:
IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
Inventor: HAYNIE DONALD T [US] Applicant: ARTIFICIAL CELL TECHNOLOGIES I
[US]
EC: C07K17/00; Y01N6/00 IPC: A61K36/06; A61K39/00; A61K9/50; (+5)
Publication US2010034875 (A1) - 2010-02-11 Priority Date: 2005-10-25 info:
POLYPEPTIDE MULTILAYER FILMS AND METHODS
Inventor: HAYNIE DONALD TEMPLETON [US]
EC: C07K17/00; Y01N6/00
Publication W02007050569 (A2) - 2007-05-03 info: W02007050569 (A3) - 2007-06-28
IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
Inventor: HAYNIE DONALD TEMPLETON [US]
EC: C07K17/00; Y01N6/00
Publication W02007050702 (A2) - 2007-05-03 info: W02007050702 (A3) - 2007-08-16
MULTILAYER FILMS, COATINGS AND MICROCAPSULES
COMPRISING POLYPEPTIDES
Inventor: HAYNIE DONALD TEMPLETON [US]
Applicant: HAYNIE DONALD TEMPLETON [US]
IPC:
Priority Date: 2005-10-25
Applicant: HAYNIE DONALD TEMPLETON [US]
IPC:
Priority Date: 2005-10-25
EC: C07K17/00; Y01N6/00
Publication W02008030253 (A2) - 2008-03-13 info: W02008030253 (A3) 2008-05-29 ־ <sup>7</sup>־Z
Applicant: LOUISIANA TECH UNIVERSITY RES [US]; HAYNIE DONALD TEMPLETON [US]
IPC: C07K17/00; C07K17/00
Priority Date: 2005-10-25
Data supplied from the espacenet database — Worldwide =1 &KC=A2&NR=2007050702A2&DB=EPODOC&locale=en EP&CC=WO&FT-D 16/09/2010
<img file="IL190885A_D0003.tif" />
<img file="IL190885A_D0004.tif" />
<img file="IL190885A_D0005.tif" />
<img file="IL190885A_D0006.tif" />
רשות הפכונסי□
מדינת ישראל משרד המשפטים
פ.ק. 27
תאריך: ה׳ תמוז תש״ע
17.06.2010
מספרכם:54797 לכבוד
סנפורד ט. קולב ושות׳ שער הגיא 4, מרמורק רחובות 76122 2273
א.ג.נ.,
1632
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הנדון: הודעה לפני קיבול בקשת פטגט מס׳ סימוכין: מלתבכם מיום 10/12/2009
<img file="IL190885A_D0008.tif" />
לתשומת לבך: מקום בו הנך מופנה לחוק׳^הכוונה היא לחוק הפטנטים,. תשכ״ז -1967. מקו
היא לתקנות הפטנטים (נוהלי הלשכה, סדת׳דין, מסמכים ואגרות), התשכ״זס - 1968.
בהתאם להוראות תקנה 41 הנני להודיעכם כי נג^צאו בבקשה הנ״ל הליקויים<img file="IL190885A_D0009.tif" />מפורטים להלן.
עליך להשיב על הודעה זו תוך ארבעה חודשים אריכה, אך הנך רשאי לבק6/את הארכת התקופה/התאם לכללים שנקבעו <img file="IL190885A_D0010.tif" />
בחוזר הרשם מ.נ. 82 (שבו ניתן לצפות באתר הרשו בעד כל חודש או חלק ממנו.
<img file="IL190885A_D0011.tif" />
ו הנך מופנה לתקנות, הכוונה
<img file="IL190885A_D0012.tif" />
עם בקשה כאמור שתוגש לפגי תום התקופה יש ל</לס אגרה בסך 61 ש״ח
הבקשה נבחנה לאחר החלפת מערכת התביעות לגא^זא 3 ואלה הליקוים .1 .2
<img file="IL190885A_D0013.tif" />
<img file="IL190885A_D0014.tif" />
לאור הסברכם ולאור צמצוק^האמצאה הנני מסיר את/יהשגות עפ״י הוראות׳קסעיפים 4 ו - 5 לקוק. בהתאם לתקנה 20(א)(1) עליכס^להזכיר בפירוט את הפר .3
<img file="IL190885A_D0015.tif" />
תוך צירוף דברי הסבר מתאימים:
מים שצוטטו כלפי הסקשה בתור ידע קודם
<img file="IL190885A_D0016.tif" />
<img file="IL190885A_D0017.tif" />
.4 .5
בוא לפירוט
<img file="IL190885A_D0018.tif" />
מערכת התביעות החדשה המוצעת מתקבלת. עליכם להביא עתו/את הגדרת האמצאה <img file="IL190885A_D0019.tif" /> לידי תיאום עם היקף התביעורלבהתאם לאעיף 3 של חוזר 23 (P).
היקף התביעות. לאח האמצאה המתוקן בשני ה
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לחוק עליכם להביא את של/האמצאה ואת כותר <img file="IL190885A_D0022.tif" /> י שם האמצאה כאמור׳לעיל יחיה עליכם להשניא עמוד שער חדש עם שם קים. ת״ל/חוזר הרשם נ. 44/בעניין זה.
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בהתאם לסעיף 12
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־/כעמוד לידי תיאום מלא עם
לאור צמצום האמצאה חורגים עז׳גה מתחומה קטעי הפירו והדגמות מסוימים. לגבי החומר שחורג לסעיף 1 של חוזר מס׳ 23 (P) של רשם הפטנטים או להשמיטו
מתחום האמצאה תוכלו לפעול בהת מהפירוט.
<img file="IL190885A_D0025.tif" />
בכבוד רב,
טוסס פר׳ 43 (3) 01.02.2010
רחוב אגודת ספורט הפועל מס׳ 1, הגן הטכנולוגי, בניין מס׳ 5, מיקוד 96951. טל׳: 5651666־2־972 פקס: 5651641־2־972
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ר/צוימת בק/צוות
<td> בקשה</td><td> פרסום</td><td> PCT</td><td> סווג</td><td> ת. בקשה |</td><td> סטטוס j ת. סטטוס</td><td> סטטוס 1</td><td> מבקש i שם אמצאה|</td><td> סימוכי</td><td> מיופה כח</td><td> <<sup>ס</sup>' !</td>
<td> לא</td><td> 2008/01</td><td> P</td><td> C12N</td><td> 113/11/2006</td><td> בבחינה[ 16/08/2010</td><td> בקשה!</td><td> !POLYPEPTID LOUISIANA</td><td> 65471</td><td> טנפור־ר ט.</td><td> !1911!</td>
<td> לא</td><td> 2008/03</td><td> P</td><td> C07K</td><td> 25/10/2006</td><td> נשלחו[ 17/08/2010</td><td> בקשה!</td><td> {MULTILAYER LOUISIANA</td><td> 65334</td><td> כונפורד ט.</td><td> !1908(</td>
<td> לא</td><td> 2006/05</td><td> □ו</td><td> A61K</td><td> ]22/11/2004</td><td> נשלחו! 13/07/2010</td><td> בקשה!</td><td> ]METHOD ]LOUISIANA</td><td> 62018</td><td> טנפור־ר ט.</td><td> 11832:</td>
ר/עימת בקצוות
<td> בקשה</td><td> פרסום</td><td> PCT</td><td> סווג</td><td> ת. בקשה |</td><td> ת. סטטוס 1</td><td> סטטוס !</td><td> סטטוס 1</td><td> שם אמצאה</td><td> מבקש</td><td> סימוכי!</td><td> מיופה כה</td><td> מסי |</td>
<td> לא</td><td> 2008/09</td><td> כו</td><td> A61K</td><td> !22/01/2008</td><td> 22/06/2010</td><td> נשלח</td><td> בקשה!</td><td> POLYPEPTID</td><td> ARTIFICIAL</td><td> 46768</td><td> ג'י.אי.ארליך</td><td> 200019</td>
<td> לא</td><td> 2007/05</td><td> כן</td><td> C07K</td><td> 25/10/2006</td><td> 11/10/2009</td><td> התקבלה</td><td> בקשהן</td><td> IMMUNOGEN</td><td> ARTIFICIAL</td><td> ן</td><td> סנפורד ט.</td><td> )190885</td>
Illllll Illi lllllllllllllllHUH IH III (12) United States Patent (10) Patent No.: US 7,615,530 B2
Haynie (45) Date of Patent: *Nov. 10,2009
US007615530B2 (54) IMMUNOGENIC COMPOSITIONS AND METHODS OFUSE (75) Inventor: Donald T. Haynie, New Haven, CT (US) (73) Assignee: Artificial Cell Technologies, Inc., New Haven, CT (US) ( * ) Notice: Subject to any disclaimer, the term of this patent is extended or adjusted under 35 U.S.C. 154(b) by 408 days.
This patent is subject to a terminal disclaimer.
(21) Appl. No.: 11/586,340 (22) Filed: Oct. 25,2006 (65) Prior Publication Data
US 2007/0077253 Al Apr. 5,2007
Related U.S. Application Data (60) Provisional application No. 60/729,828, filed on Oct. 25, 2005.
(51) Int. Cl.
A61K 38/00 (2006.01) (52) U.S.C1............... 514/2; 530/802; 530/300 (58) Field of Classification Search ............ None
See application file for complete search history.
(56) References Cited
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Boura, et al; “Endothelial Cells Grown on Thin Polyelectrolyte Mutilayered Films: An Evaluation of a New Versatile Surface Modification”; Biomaterials; 24; pp. 3521-3530; 2003.
Chluba et al; “Peptide Hormone Covalently Bound to Polyelectrolytes and Embedded into Mutilayer Architectures Conserving Full Biological Activity”; Biomacromojecules; 2; pp. 800805;2001.
Glinel, et al.; Polyelectrolyte Multilayers Based on Amphiphilic Polysaccharides: Application for Entrapment and Release of Hydrophobic Molecules”; Abstracts of Papers American Chemical Society, 230, p. U3590; 2005; Abstract.
Haynie, et al.; “Protein-Inspired Multilayer Nanofilms: Science, Technology and Medicine”; Nanomedicine: Nanotechnology, Biology, and Medicine; 2; pp. 150-157; 2006.
Jessel, et al; “Bioactive Coatings Based on Polyelectrolyte Multilayer Architecture Functionalized by Embedded Proteins”; Adv. Mater.; 15; pp. 692-695; 2003.
Lavalie, et al; “Comparison of the Structure of Polyelectrolyte Multilayer Films Exhibiting a Linear and an Exponential Growth Regime: An in Situ Atomic Force Microscopy Study”; Macromolecules; 35; pp. 4458-4465; 2002.
Li, et al.; “Multilayer Biomimetics: Reversible Covalent Stabilization of a Nanostructured Bio film”; Biomacromolecules; 5; pp. 16671670; 2004.
Picart, et al; Buildup Mechanism for Poly(L-lysine)/Byaluronic Acid Films onto a Solid Surface”; Langmuir; 17; pp. 7414-7424; 2001.
(Continued)
Primary Examiner—Cecilia Tsang Assistant Examiner—Christina Bradley (74) Attorney, Agent, or Firm—Cantor Colburn LLP (57) ABSTRACT
Disclosed herein are immunogenic compositions comprising a multilayer film comprising two or more layers of polyelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes. A first layer polyelectrolyte comprises an antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the antigenic polypeptide and the one or more surface adsorption regions have the same polarity. The immunogenic compositions may be employed in methods of eliciting an immune response in a vertebrate organism.
Claims, 4 Drawing Sheets
US 7,615,530 B2
Page 2
OTHER PUBLICATIONS
Picart, et al; “Molecular Basis for the Explanation of the Exponential Growth of Polyelectrolyte Multilayers”; PNAS; 22; pp. 1253112535; 2002.
Richert, et al; Cell Interactions with Polyeletrolyte Multilayer Films; Biomacromolecules; 3; pp, 1170-1178; 2002.
Tryoen-Toth, et al; “Viability, Adhesion, and Bone Phenotype of Osteoblast-like Cells on Polyelectrolyte Multilayer Films”; J. Biomed. Mater. Res.; 60; pp. 657-667; 2002.
Vautier, et al. “Polyelectrolyte Multilayer Films Moldulate Cytoskeletal Oranization in Chondrosarcoma Cells”; J. Biomater. Sci. Polymer Edn.; 13; pp. 713-732; 2002.
Zheng, et al.; “Design of Peptides for Thin Films, Coatings and Microcapsules for Applications in Biotechnology”; Journal of Biomaterials Science Polymer Edition 05; 16; pp. 285-299; 2005.
International Search Report; International Application No. PCT/ US2006/041666; International Filing Date Oct. 25, 2006; Applicant’s File Reference; Date of Mailing Jul. 4, 2007; 8 pages.
Written Opinion of International Searching Authority; International Application No. PCT/US2006/041666; International Filing Date Oct 25,2006; Applicant’s File Reference PCT/ISA/220; Date of Mailing Jul. 4, 2007; 9 pages.
Boulmedais et al.; “Buildup of Exponentially Growing Multilayer Polypeptide Films with Internal Secondary Structure”; Langmuir; 19; pp. 440-445; (2003).
Alcaro et al; Synthetic Peptides in the Diagnosis of HIV Infection”; Current Protein and Peptide Science; 4; pp. 285-290; (2003).
Ben-Yedidia et al; Design of Peptide and Polypeptide Vaccines”; Current Opinion in Biotechnology; 8; pp. 442-448; (1997).
Brown et al; “Optimisation of a Peptide-Based Indirect ELISA for the Detection of Antibody in the Serum of HIV-1 Seropositive Patients; Journal of Immunological Methods; 200; pp. 79-88; (1997).
Decher, Gero; Fuzzy Nanoassemblies: Toward Layered Polymeric Multicomposites”; Science; 277; pp. 1232-1237; (1997).
Giuliani et al; “A Universal Vaccine for Serogroup B Meningococcus”; Proc. Natl. Acad. Sci. USA; 103; pp. 10834-10839; (2006).
Humphreys et al; “Synthetic Peptide Vaccine Against Pandemic H5N1 Influenza Based on li-Key Modified MHC Class II Epitopes”; Pharmaceutical Discovery & Development; May/Jun. 2006; pp. 25, 26 and 29; (2006).
Iler, R. K.; “Multilayers of Colloidal Particles”; Journal of Colloid and Interface Science; 21; pp. 569-594; (1966).
Lvov, Y. et al; “Electrostatic Layer-by-Layer Assembly of Proteins and Polyions; Protein Architecture: Interfacial Molecular Assembly and Immobilization Biotechnology; CRC Press; New York; 15281997; pp. 125-167; ISBN: 0824782364; (1999).
Lvov, Y. et al; “Urease Encapsulation in Nanoorganized Microshells”; Nano Letters; 1; pp. 125-128; (2001).
* cited by examiner
US 7,615,530 B2
-continued <400> SEQUENCE: 12
Lys Lys Lys Ala Lys Lys Lys Gly 15
Asn Ala Lys Ala Thr Tyr Glu Ala
Leu Ala Ala Vai Lys Lys Ala Asn
3540
Glu Asn Thr Ala lie Lys Gin Arg 5055
Lys Lys Ala Lys Lys Lys Gly Lys 6570
Lys Lys Lys Ala Lys Lys Lys Gly
1015
Ala Leu Lys Gin Tyr Glu Ala Asp
2530
Ala Ala Gly Ala Ala Leu Thr Ala 45
Asn Glu Asn Ala Lys Ala Gly Lys
Lys Lys Ala Lys Lys Lys Gly 75
The invention claimed is:
1. A multilayer film comprising two or more layers of 20 polyelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes, wherein a first layer polyelectrolyte comprises a first antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more 25 antigenic determinant regions, wherein the first antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one 30 or more amino acid sequence motifs consisting of 5 to 15 amino acid residues and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to about 250 amino acid residues, and one or 35 more antigenic determinant regions comprises a viral antigen, wherein the first antigenic polypeptide is an unbranched polypeptide, is not a homopolymer, is at least 15 amino acid residues long, and has an aqueous solubility at pH 4 40 to 10 of greater than 50 pg/ml;
wherein a second layer comprises a second layer polyelectrolyte comprising a polycationic material or a polyanionic material having a molecular weight of greater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide.
2. The multilayer film of claim 1, wherein the first antigenic polypeptide is in the exterior layer of the multilayer film.
3. The multilayer film of claim 1, wherein the first antigenic polypeptide comprises two or more antigenic determinants.
4. The multilayer film of claim 3, wherein the two or more antigenic determinants are from the same or different pathogen or target disease.
5. The multilayer film of claim 1, further comprising a second antigenic polypeptide comprising one or more second surface adsorption regions covalently linked to one or more second antigenic determinant regions, wherein the second antigenic polypeptide and the one or more second surface adsorption regions have the same polarity, wherein the one or more second surface adsorption regions comprises one or more second amino acid sequence motifs, the one or more second amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and 65 wherein the one or more second antigenic determinant regions comprises 3 to about 250 amino acid residues, wherein the second antigenic polypeptide is not a homopolymer, is at least 15 amino acids long, and has an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml.
6. The multilayer film of claim 5, wherein the one or more first antigenic determinant regions and the one or more second antigenic determinant regions are from the same or different virus.
7. The multilayer film of claim 1, further comprising a drug, an oligonucleotide, a nucleic acid, a lipid, a phospholipid, a carbohydrate, a polysaccharide, a lipopolysaccharide, or a combination of one or more of the foregoing molecules.
8. The multilayer film of claim 1, wherein the antigenic polypeptide has an aqueous solubility of greater than or equal to about 1 mg/mL.
9. The multilayer film of claim 1, wherein the one or more antigenic determinant regions comprises an antigenic motif comprising 3 to about 50 amino acid residues, and wherein the first antigenic polypeptide has a magnitude of charge per residue at neutral pH of greater than or equal to 0.4.
10. The multilayer film of claim 1, wherein the one or more antigenic determinant regions is an antigenic domain comprising about 50 to about 250 amino acid residues.
11. The multilayer film of claim 10, wherein the antigenic domain has a water solubility at pH 4 to 10 of greater than 50 pg/mL.
12. The multilayer film of claim 1, wherein the multilayer film encapsulates one or more non-peptide molecules.
13. The multilayer film of claim 1, wherein the multilayer film is in the form of a microcapsule.
14. The multilayer film of claim 13, wherein the microcapsule comprises a core comprising a drug, a protein, an oligonucleotide, a nucleic acid, a lipid, a phospholipid, a carbohydrate, a polysaccharide, a lipopolysaccharide, or a combination of one or more of the foregoing molecules.
15. A method of eliciting an immune response in a vertebrate organism comprising administering into the vertebrate organism composition comprising, a multilayer film comprising two or more layers of polyelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes, wherein a first layer polyelectrolyte comprises a first antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consi sting of 5 to 15
US 7,615,530 B2 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to about 250amino acid residues, andoneor more antigenic determinant regions comprises a viral antigen, wherein the antigenic polypeptide is an unbranched polypeptide, is not a homopolymer, is at least 15 amino acid residues long, and has an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml;
wherein a second layer comprises a second layer poly electrolyte comprising a polycationic material or a polyanionic material having a molecular weight of greater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide.
16. The method of claim 15, wherein the multilayer film is administered intramuscularly or subcutaneously.
17. A method of making a multilayer film, the method comprising:
depositing a first layer polyelectrolyte on a surface of a substrate to form a first layer; wherein, the first layer polyelectrolyte comprises a first antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the first antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to about 250 amino acid residues, and one or more antigenic determinant regions comprises a viral antigen, wherein the first antigenic polypeptide is an unbranched polypeptide, is not a homopolymer, is at least 15 amino acid residues long, and has an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml;
depositing a second layer polyelectrolyte on the first layer polyelectrolyte to form a second layer; wherein a second layer comprises a second layer polyelectrolyte comprising a polycationic material or a polyanionic material having a molecular weight of greater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide.
18. The multilayer film of claim 1, wherein the first antigenic polypeptide is an unbranched polypeptide.
19. The multilayer film of claim 1, wherein the one or more surface adsorption regions is non-homopolymeric.
20. The multilayer film of claim 1, wherein the viral antigen is selected from the group consisting of an HIV-1 antigen: a hepatitis A, B or C antigen; an influenza virus antigen; a measles viral antigen; a rubella virus antigen; a rotavirus antigen; a cytomegalovirus antigen; a respiratory syncytial viral antigen; a herpes simplex viral antigen; a varicella zoster virus antigen; a Japanese encephalitis virus antigen; and a rabies virus antigen.
*****
XP008078451
J Biomater. Sci. Polymer Edn, Vol. 16, No. 3, pp. 285 —299 (2005) © VSP 2005.
Also available online ־ www.vsppub.com
Design of peptides for thin films, coatings and microcapsules for applications in biotechnology
BIN ZHENG <sup>1</sup>, DONALD T. HAYNIE<sup>2</sup>'<sup>3</sup>’*, HUA ZHONG<sup>4</sup>,
KAUSTUBH SABNIS <sup>4</sup>, VINAY SURPURIYA<sup>5</sup>.**, N1KHEL PARGAONKAR , GYANESH SHARMA <sup>2</sup> and KRANTHI VISTAKULA <sup>2</sup><sup>1</sup> Computational Analysis and Modeling, College of Engineering and Science,
Louisiana Tech University, Ruston, LA. 71272, USA , <sup>2</sup> Biomedical Engineering Faculty, Institute for Micromanufacturing, Louisiana. Tech University, PO Box 10137, Ruston, LA 71272. USA <sup>3</sup> Physics, College of Engineering and Science, Louisiana Tech University,
Ruston, LA 71272, USA . .
<sup>4</sup> Computer Science, College of Engineering and Science, Louisiana Tech University,
Ruston, LA 71272, USA <sup>5</sup> Electrical Engineering, College of Engineering and Science,
Louisiana Tech University, Ruston, LA 71272, USA
Received 11 February 2004; accepted 24 May 2004
Abstract__A highly-interdisciplinary approach has been developed for minimizingdfae.imi'DunQgeriic ,״.
ity of films, coatings, microcapsules and other nano-structured materials fabricated from designed polypeptide chains. It is to base the amino-acid sequences on solvent-exposed regions in the folded states of proteins from the same organism. Each such region that meets defined criteria with respect to charge is called a sequence motif. The approach becomes more specifically tailored for intravenous applications by requiring an employed sequence motif to correspond to a known blood protein. An algorithm has been developed to identify sequence motifs in protein-encoding regions of a genome^h!^ work is focused on sequence motifs of charge per unit length >0.5 at n^al_P^2t_has_been found ~thattitekd1nb־er oHmiqiie sequence motifs meeting this criterion in available human genomd data is maximal for motifs of approx, 7 residues in length. We have designed polypeptides on the basis o computational analysed shown that they can be tiied to fabricate nano-structured thin films by electrostatic layer-by-layer assembly (ELBL). The results of this work are discussed with a view to possible applications in biotechnology, notably development of biocompatible coatings and microcapsules.
Key words׳ Antigenicity; biocompatibility; bionanotechnology; computer-aided design; data mining; human genome; immunogenicity; layer-by-layer assembly; secondary structure propensity.
*To whom correspondence should be addressed. Tel.! (1-318) 257-3790. Fax: (1-318) 257-5104.
E-mail; haynie@coes.latech.edu ־*Present address; Department of Electrical and Computer Engineering, University of Illinois at Chicago.
BNSDOCID: <XP 807B461A_J_>
XP008078451
286 Bin Zheng et al.
INTRODUCTION
A protein is more or less immunogenic, depending on the extent to which its structural features are recognized by the immune system as ‘foreign’ [1]. A single foreign protein will ordinarily have several epitopes of different degrees of immunogenicity. Various attempts have been made to determine the structural basis of the immune response to a given polypeptide. Such research is complicated by the variability of individuals within a population, though it is generally agreed that the rules of immunogenicity are mostly universal for a given species.
Conventional wisdom for maximizing polypeptide immunogenicity is as follows: keep predicted hydrophobicity low and predicted hydrophilicity, backbone flexibility, surface accessibility, antigenicity and odds of j8-turn formation high [2]. It would seem that standing these rules on their head could help to minimize the immunogenicity of a designed peptide.
A variety of tools are used to select a polypeptide immunogen. One approach is to calculate sequence hydrophobicity using Fauchere-Pliska [3] or Hopp-Woods [4, 5] and then to predict second structure content using Chou—Fasman [6, 7]. One could then select for hydrophilic sequences that are also predicted to be turns. For some researchers, however, surface probability, antigenicity index and hydrophilicity are the most important considerations. Hydrophilicity could be estimated by Hopp-Woods [5] or Kyte-Doolittle [8], antigenicity by Jameson-Wolf [9], surface probability by Emini et al. [10] and propensity to form turn or coil by Garnier et al. [11]. Important for the present work, the average distribution of charge might also be relevant to immunogenicity.
One of several points of dispute in the prediction game for generating antibodies is the ideal length of a peptide. Most peptide antigens range in length from 12 to 16 residues, though peptides 9 residues or shorter can be effective immunogens [12]. Peptides longer than 12-16 amino acids may contain multiple epitopes. It thus would seem that to minimize antigenicity one should prefer a peptide shorter than 12 residues, or even better 9 residues. Such a short polypeptide probably would not form a stable secondary structure in solution. This may be important for controlling the formation of supramolecular polypeptide structures, notably films, coatings and microcapsules.
ELBL is a platform methodology of nanomanufacturing. It can be used to create films, coatings and microcapsules of defined thickness on the nanometer scale. The approach was pioneered by Iler [13] nearly four decades ago using colloidal particles, based on earlier work by Langmuir [14]. More recently, the general method was rediscovered by Decher and co-workers, who have used non-biological polyelectrolytes as a material for assembly [15]. Proteins too have been used to form multilayer films by ELBL (reviewed in Ref. [16]). In all such cases, a key driving force governing adsorption and assembly behavior is electrostatic attraction (Fig. 1). ‘Secondary interactions’, however, such as hydrogen bonding, van der Waals interactions and hydrophobic interactions, can also be important to the film
BNSDOCID: <XP 8078461A_L>
XP008078451
Polypeptide bionanotechnology
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Figure 1. Schematic diagram of ELBE. (A) Planar surface. Thin films of oppositely charged linear polymers are assembled in successive layers on a negatively-charged, planar surface. Looselybound material is rinsed away following an adsorption step. The surface charge is reversed after the deposition of each layer. Each layer has a thickness on the order of a few nanometers, the average depending on the type of polymer and conditions of assembly. Multilayer assemblies of precisely repeatable thickness can be obtained. (B) Spherical surface. Multilayers □f polyelectrolyte are formed as in the planar case, A suitable choice of support enables microcapsule fabrication on change of conditions. Polyelectrolytes are assembled to create concentric shells of alternating charged polymers. Following assembly of the desired number of layers, the support is dissolved. This figure is published in colour bn http'.Z/www.ingenta.com fabrication process (reviewed in Ref. [17]), particularly when the net charge on a polymer is relatively low.
There has been substantial and growing interest in developing ELBL using polyelectrolytes during the last decade [15]. Relatively little, however, is known about how members of the rather special class of polyelectrolyte called polypeptides might be useful for ELBL [18-20], despite considerable interest in employing proteins for this purpose (reviewed in Ref. [16]). In recent studies we have shown that assembly behavior of polypeptides in ELBL is influenced by pH, chain length, salt concentration and secondary structure content [21] and that film stability depends on a post-preparation treatment (data not shown). We have also used polypeptides to develop anti-microbial thin films by ELBL (data not shown).
This work presents criteria for designing polypeptides for fabrication by ELBL of polypeptide films, coatings and microcapsules for applications in biotechnology.
XP008078451
2gg Bin Zheng et al.
We describe how the design criteria have been applied to the development of a computer-based methodology for identifying ‘sequence motifs’ in amino-acid sequence infoimation. A sequence motif is a design element of a polypeptide intended to optimize the physical, chemical and biological properties of structures fabricated by ELBL. The length of a peptide motif has been set to 7 to optimize control over physical structure in solution, number of non-redundant sequence motifs in available amino-acid sequence data and immunogenicity. We provide experimental proof that amino-acid sequence designs compatible with the criteria are useful for ELBL. This work also touches on applications of the technology.
MATERIALS AND METHODS
Protein sequence information y\21 non-redundant amino-acid sequence information curient and available in autumn 2001 from the National Center for Biotechnology Information (NCBI; http:// www.ncbi.nlm.nih.gov) was obtained for this work. To simplify analysis, several original computer programs were developed to identify all sequences from Homo sapiens in the original NCBI database file and to extract and write them to a separate text file [22].
Determination of the number of unique sequence motifs
The H. sapiens data were analyzed to determine the number of contiguous residues corresponding to the largest number of unique amino-acid sequences. Each sequence meeting specific criteria was called a sequence motif. The criteria by which a motif was identified were as follows; (1) all charged residues in a test sequence at neutral pH must be either acidic (Asp or Glu) or basic (Arg, Lys or His) and (2) at least half of the residues in a test sequence must be charged at neutral pH.
The second design criterion is intended to increase the odds of suitability of the sequence for ELBL. In identifying motifs in NCBI sequence data only the 20 usual amino acids were considered. A schematic diagram of the algorithm used is given in Fig. 2. The process of searching for a negatively-charged motif in sequence data can be described as follows. First, an amino-acid residue is selected. Second, this amino acid and the following 6 residues are examined for occurrences of Arg, His or Lys. Third, if one or more Arg, His, or Lys residues is found in the 6 these 7 amino-acid residues, the process is begun anew at another amino acid. If, however, no Arg, His, or Lys is found, the 7 residues are examined to determine the number of occurrences of Glu and/or Asp. Fourth, if there are at least 4 occurrences of Glu and/or Asp in the 7 residues, the sequence motif is cataloged as a motif. Fifth, the process is begun anew at another amino acid. If, however, fewer than 4 occurrences of negative charged amino acids are found, the process is begun at the amino acid immediately adjacent to the one just examined. The selection process is exactly the
BNSDOCID: <XP_______ΒΟ7Θ451Α_Λ>
XP008078451
Polypeptide bionanotechnology
<img file="IL190885A_D0034.tif" />
Figure 2. Flow chart of the process to extract protein motifs from amino-acid sequence data.
same for positively charged amino acids, except that Glu and Asp are replaced by Arg, His and Lys. In this work the same approach was used to determine the number of unique motifs for all given lengths of motif.
Development of the sequence motif library for polypeptide design
All unique sequence motifs were deposited in an Oracle 82 database. The data stored were motif ID, motif sequence, various computed secondary propensity values, computed hydrophobicity, computed hydrophilicity and computed surface probability. A custom graphical user interface has been developed [23] to simplify access to motif information and assessment of its suitability for a particular application (Fig. 3).
Protein structure
A number of physical properties of amino-acid sequences were considered as the basis for rank-ordering the identified motifs. Secondary structure propensities, for example, were calculated using the approach of Chou and Fasman [6]. More than 2500 high-resolution X-ray crystallographic structures (1334 containing a-helices and 1221 containing ^-sheets) were selected from the Protein Data Bank (PDB) on the basis of method of structure determination (X-ray diffraction), resolution (better than 2.0 A) and structural diversity (less than 50% sequence identity between the protein crystallographic structures used to compute the helix and sheet propensities of the various amino acids). The rationale was to choose high-resolution structures determined by the most reliable method available and not to bias the analysis by too many similar structures. Secondary structure propensity of a sequence motif was
BNSDOCID: <XP_______B07B451A—1_>
XP008078451
Bin Zheng et al.
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Design of polypeptides for ELBL
The methodology is based on several concerns. One, the electrostatic properties of the peptides must be compatible with the basic principle of ELBL. This point is perhaps the most important one, because it is the basis of ELBL. Two, the peptides should exhibit minimal secondary structure in aqueous solution. Structural
BNSDOCID: <XP_______B078451A__l_>
XP008078451
Polypeptide bionanotechnology 291 properties of the peptides in solation determine to some extent the physical properties of the film [21]. Three, the physical stability of the films will presumably depend on properties of the peptides and details of the fabrication process (data not shown). And four, the biocompatibility and bioactivity of the peptides and peptide films, coatings and microcapsules will depend on the structure of the peptides [1]. The first two points are general concerns; the last two are mainly a matter of the intended application of the ELBE films. In addition, polypeptide design for ELBL will generally consider a number of structural preferences. Examples include the amino-acid link between sequence motifs in the polypeptide chain. In the present work, Gly served as linker to minimize secondary structure formation and inhibit turn formation. Cys could be used to cross-link polypeptide layers in an ELBL film (Ref. [24] and data not shown). Polypeptides designed on the basis of identified motifs and synthesized for this work were:
Sequence 1 (SN1)
Γ<sup>,</sup>Tyr Glu Glu Asp Glu Cys Gin Asp Gly Glu Glu Asp Glu Cys Gin Asp Gly Glu Glu ־ L Asp Glu Cys Gin Asp Gly Glu Glu Asp Glu Cys Gin Asp
Γ Sequence 2 (SP2) ׳Tyr Arg Arg Arg Arg Ser Vai Gin Gly Arg Arg Arg Arg Ser Vai Gin Gly Arg Arg Arg Arg Ser Vai Gin Gly Arg Arg Arg Arg Ser Vai Gin
Sequence 3 (LN3) !״־Tyr Glu Glu Asp Glu Cys Gin Asp Gly Glu Glu Asp Glu Cys Gin Asp Gly Glu Glu I / Asp Glu Cys Gin Asp Gly Glu Glu Asp Glu Cys Gin Asp Gly Glu Glu Asp Glu / Cys Gin Asp Gly Glu Glu Asp Glu Cys Gin Asp
ΓSequence 4 (LP4)
Tyr Arg Arg Arg Arg Ser Vai Gin Gly Arg Arg Arg Arg Ser Vai Gin Gly Arg Arg Arg Arg Ser Vai Gin Gly Arg Arg Arg Arg Ser Vai Gin Gly Arg Arg Arg Arg Ser Vai Gin Gly Arg Arg Arg Arg Ser Vai Gin
Sequences 1 and 2, SN1 and SP2, are 32-mers; sequences 3 and 4, LN3 and LP4, are 48-mers; the positive and negative peptide motifs were repeated 4 times for the short polypeptides and 6 times for the long ones. The Gly linker residues, shown in bold, are intended to inhibit secondary structure formation. The N-terminal Tyr is for spectroscopic detection and quantification of peptide concentration in aqueous solution.
Polypeptide ELBL
SN1, SP2, LN3 and SP4 were obtained in lyophilized form from a commercial source, and the mass and purity of each peptide was verified by electrospray mass spectrometry (not shown). The peptides were used without further purification. Each peptide was dissolved in 10 mM phosphate buffer, pH 7.4 or 10 mM Tris, pH 7.4 to a final concentration of 2 mg ml<sup>1</sup>־־ and the adsorption time was 20 mm.
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Peptide multilayer assembly at room temperature was monitored by quartz crystal microbalance (QCM) [25]. Resonators were from Sanwa Tsusho (Japan). The rinsing solution was deionized water. Following polyelectrolyte adsorption, each sample was dried using a stream of dry gas, nitrogen or air. The film fabrication process was as follows: (1) prepare solutions of peptides as described above;
(2) immerse the QC!M resonator sequentially in each of these solutions foi 20 min, (3) rinse the resonator for several seconds after each adsorption step; (4) dry the resonator in a stream of gas; (5) monitor the deposition of material by QCM. Resonator frequency shift, Δ/, can be converted to mass increment of adsorbed material as Am(ng) ™ 0.87 x Δ/ (Hz) (see, for example, Ref. [16]).
RESULTS
Computational analysis revealed that 87 779 H. sapiens sequences were in the nonredundant NCBI protein sequence database in autumn 2001. This information was used to calculate the number of unique motifs of 2 15 residues in length. The minimum numbers of positively- or negatively-charged residues for a given motif length are given by Table 1. Figure 4 shows the number of non-redundant sequence motifs identified. The greatest number of positive motifs was found for 5 residues, the greatest number of negative motifs for 7 residues. The number of non-redundant positively- and negatively-charged heptameric motifs was 54 251 and 27 226, respectively. All such motifs have been deposited in a relational database [22] for access using a custom-designed graphical user interface (Fig. 3).
The secondary structure propensity values for the amino acids in Sequences 1-4, calculated as described in the Materials and Methods section, are tabulated in the third and fifth columns of Table 2. Proline was found to have the lowest a-helix and /3-sheet propensity values (data not shown). These values were used to calculate the secondary structure propensity of each identified motif. Other physical properties were calculated, e.g., hydrophobicity, hydrophilicity, surface accessibility and net charge at neutral pH, using Kyte-Doolittle [8] and Emini et al. [10]. Such data can be used to rank order motifs for peptide design, depending on the weighting factor assigned to each property.
Figure 5 shows the distribution of secondary structure propensities for all identilled H. sapiens sequence motifs. The distributions are, curiously, triangular in
Table 1.
Minimum, number of charged amino acids for a given motif length
Motif length 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15
Minimum, number of 1 223344556 6 7 7 8 8 charged residues of the same sign at neutral pH _______
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<img file="IL190885A_D0036.tif" />
Figure 4. Number of unique sequence motifs versus size of motif. Squares, positive motifs; diamonds, negative motifs. This figure is published in colour on http://www.ingenta.com
Table 2.
Computed secondary structure frequencies and propensities
<td> Amino acid</td><td> F<sub>a</sub></td><td> Pa</td><td></td><td> Ρβ</td>
<td> Arg</td><td> 0.44</td><td> 1.17*</td><td> 0.18</td><td> 0.82</td>
<td> Asp</td><td> 0.35</td><td> 0.94</td><td> 0.14</td><td> 0.61</td>
<td> Cys</td><td> 0.33</td><td> 0.88</td><td> 0.27</td><td> 1.20</td>
<td> Gin</td><td> 0.45</td><td> 1.21</td><td> 0.18</td><td> 0.79*</td>
<td> Glu</td><td> 0.48</td><td> 1.27</td><td> 0.16</td><td> 0.74*</td>
<td> Gly</td><td> 0.25</td><td> 0.65</td><td> 0.17</td><td> 0.76</td>
<td> Lys</td><td> 0.42</td><td> 1.13</td><td> 0.18</td><td> 0.80</td>
<td> Ser</td><td> 0.35</td><td> 0.92</td><td> 0.20</td><td> 0.89</td>
<td> Tyr</td><td> 0.37</td><td> 0.98</td><td> 0.29</td><td> 1.30</td>
<td colspan="4"> F and P are the frequency and propensity value for each amino acid in an a indicated. * Significant difference from the conesponding Chou-Fasman value [6, 7].</td><td> -helix or β-sheet, as</td>
shape. The rectangle highlights the sequence motifs least likely to form secondary structure in aqueous solution; an important polypeptide design criterion.
Sequences 1-4 were synthesized, purified and tested experimentally for suitability in ELBL. Representative results, shown in Fig. 6, indicate that multilayer films were formed on alternative adsorption of tiie charged polypeptides: Each successive adsorption step resulted in a decrease in the resonant frequency of the QCM resonator. The decrease in frequency was approximately linear.
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XP008078451
Bin Zheng et al,
<img file="IL190885A_D0037.tif" />
<img file="IL190885A_D0038.tif" />
Helix propensity
Figure 5. Distribution, of secondary structure formation propensities in sequence motifs. Light shading, non-redundant random sequences produced using a random number generator using a PC; white, non-redundant basic sequence motifs identified in human amino-acid sequences; datk shading, non-redundant acidic sequence motifs identified in human amino-acid sequences; shaded 1 ectangle, region of the distribution least likely to form secondary structure in aqueous solution. This figure is published in colour on http://www.ingenta.com
DISCUSSION
PH .RT. is an established technique in which ultrathin films are assembled by sequential adsorption of oppositely-charged poly electrolytes (see, for example, Ref. [26]). The process is based on reversal of surface charge of the film after deposition of each layer. The resulting layers can have a thickness as small as a few nanometers; one has considerable control over the film assembly process. Deposition is repeated by alternating the charge of the adsorbing species until a film of desired overall thickness is formed. Because of the generality and relative simplicity of the process, ELBL permits the deposition of an extremely broad range of materials onto a comparable variety of surfaces. Therefore, there is a vast range of possible useful combinations of materials and surfaces. The methodology advanced here is primarily intended for applications in biotechnology.
A number of synthetic polyelectrolytes have been employed in ELBL applications, for example, sodium polystyrene sulfonate), poly(allylamine hydrochloride) and poly(vinylsulfonic acid). Such materials, however, are not generally useful for
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XP008078451
<img file="IL190885A_D0039.tif" />
Figure 6. Formation of multilayers of designed polypeptides as monitored by quartz crystal microbalance. Resonator frequency is plotted versus adsorbed layer. Adsorption characteristics are shown of different combinations of SP1, SN2, LP3 and LN4 in 10 mM sodium phosphate (pH 7.4) or 10 mM Tris (pH 7.4). The lines merely connect experimental data points. It is evident that sequential adsorption steps resulted in corresponding decreases in resonant frequency, indicating increases in deposited peptide and multilayer formation.
biomedical applications because they may be toxic if not immunogenic. Certain knowledge of the biological concerns can only be obtained empirically.
Proteins are natural polymers, suggesting that they might be useful for films, coatings, or microcapsules in biomedical applications. This is indeed the case, because in a soluble protein many side chains will have an ionizable group. Examples of proteins that have been used in ELBL include cytochrome c, hen egg white lysozyme, immunoglobulin G, myoglobin, hemoglobin and serum albumin (reviewed i n Ref. [16]).
Proteins, however, present a number of difficulties for ELBL. These include limited control over multilayer structure (because the surface of a protein is highly irregular and proteins will not readily adsorb on a surface in a regular pattern), restrictions on pH due to the pH-dependence of protein solubility and structural stability, possible antigenicity or some of othei form of bioincompatibility when using exogenous proteins and the cost of scaling up film fabiication if the corresponding gene has not been cloned, making a protein effectively unaffordable for large-scale production. These obstacles, however, can be circumvented using polypeptides based on human genome data.
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Polypeptides constitute a distinctive class of materials for ELBL. A polypeptide is generally smaller and less complex than a protein. Polypeptide film structures formed by EL.־RT. are likely to be useful in a broad range of applications. We have introduced the concept of designing peptides to exhibit several useful properties, including completely determined primary structure, minimal secondary structure in solution, monodispersity, completely controlled net charge per unit length, ability to form reversible cross-links on demand, ability to form better-controlled thin films than protein and modest large-scale production cost [21]. Possible applications range from biomedical technology to food technology to environmental technology. Control of polypeptide structure will be important for applications in which immunogenicity is a concern.
The second motif identification criterion given in the Materials and Methods section ensures that a designed polypeptide will be sufficiently soluble in aqueous solvent and have a sufficient net charge to be useful for ELBL. Proof that a charge per unit length of 0.5 is suitable for ELBL is provided by Fig. 6. One can easily imagine, however, that although the charged residues in a motif should ordinarily be of the same sign, as in conventional poly electrolyte ELBL (see, for example Refs [16, 26]), such a restrictive condition is not absolutely necessary. Experimental proof of this is that a folded protein with both positive charges and negative charge? can be used for ELBL (Ref. [16] and data not shown). Optimal control of the assembly process, however, requires a large charge per unit length. It should be noted that although the motif identification criteria were developed for amino-ack sequence analysis, they could also be employed for de novo design of peptides fo: ELBL, as we have done in a study of the role of disulfide bond formation in th< stabilization of polypeptide multilayer thin films (data not shown).
The NCBI protein sequence database has been updated frequently since autumi 2001, when the data for these calculations were obtained from the Center. Th< method described here, however, is independent of the number of sequences in th< library. Moreover, it is independent of whether the database contains redundancies Furthermore, it is independent of the choice of length of motif. In cases when a means is available for translation of genetic information, a nucleotide sequence will be just as useful for this work as an amino-acid sequence. The approacl is also equally valid for any species: We have focused on H. sapiens out o interest in human medicine, but the same approach could be used, say, for equin veterinary medicine. Human blood proteins might make particularly useful source of sequence motifs for polypeptides for intravenous applications. Such polypeptide could be used, for example, to fabricate microcapsules for use as artificial red bloo׳ cells [27] (see Ref. [28] for a recent review of blood substitutes), drug deliver devices (see, for example, Ref. [29]), or antimicrobial films (Ref. [30] and data nc shown). It is not hard to imagine that vesicles made of amino acids could be a altogether more useful product for drug delivery than ones made of liposomes.
The greatest number of unique positive and negative motifs in the human sequenc information accessed in autumn 2001 was for a motif length of 7 residues (299 mor
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Polypeptide bionanotechnology 297 motifs than for 5 residues). It is possible that the motif length giving to the greatest number of positive and negative motifs would be slightly different if a different charge selection criterion were used. A length of 6 is a likely possibility.
The number of non-redundant positively-charged 7-residue motifs (54 117) was expected to be greater than the number of negatively-charged 7-residue motifs (27 115). Of the several possible reasons for this, the main one is that there are three basic amino-acid types (Arg, Lys and His) but only two acidic types (Asp and Glu). The number of possible combinations thus is greater for positive motifs than negative ones.
The length of a peptide motif was set to 7 to minimize secondary structure formation and optimize biocompatibility. Secondary structure formation decreases control of the physical structure of the polypeptides and films made from them (data not shown). This is the reason why secondary structure propensity is calculated for each motif.
There is good agreement between our calculated secondary structure propensities and those of Chou and Fasman [6, 7]. !?here are, however, some notable differences. In particular, the o׳-helix propensity of Arg has increased from 0.79 to 1.17. The β-sheet propensity of Gin has decreased from 1.23 to 0.79, while that of Glu is increased from 0.26 to 0.74. Such discrepancies are not surprising in view of the small number of protein structures available to Chou and Fasman in the mid-1970s. Moreover, such differences might help to explain the relatively low accuracy of secondary structure predictions based on Chou—Fasman parameters: approx. 50% for a-helix, approx. 40% for /3-sheet and approx. 65% for coil. Because our secondary structure propensities closely resemble those of another recent report [31], it seems that placing confidence in predications based on nowoutdated Chou-Fasman parameters [6, 7] should be avoided. Difficulties related to specific values of Chou-Fasman parameter values, however, do not undermine the cogency or suitability of the basic approach to peptide design outlined here.
The QCM data shown in Fig. 6 indicate that the polypeptides involved formed multilayers. Linear adsorption has been noted by other researchers and studied in some depth (see, for example, Ref. [32]). This seems to indicate precise assembly of polymer during adsorption and an approximately uniform density of peptides. Other polypeptides have been designed using the criteria outlined above and found to be well suited to multilayer film fabrication (data not shown). No peptide has been designed using the criteria and found not to be suitable for ELBL.
CONCLUSIONS
A novel method of designing polypeptides for the fabrication of novel nanoorganized structures has been presented. The approach integrates a broad range of disciplines. The peptides identified by the selection method have been shown suitable for ELBL and, therefore, for the nanofabrication of thin films, coatings and microcapsules for applications in biomedicine and other fields. Aspects of the
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design and fabrication cycle could be automated, important for futuie developments and prospects for commercialization. For example, a computer algorithm could be used to optimize the primary structure of peptides for ELBL by comparing predicted peptide properties with observed physical properties, including structure in solution, adsorption behavior and film stability at extremes of pH. Moreover, the polypeptide film assembly process could be mechanized, once details of the various steps have been sufficiently determined.
Acknowledgements
This work was supported by a seed grant from the Center for Entiepreneurship and Information Technology (CEnlT), Louisiana Tech University. CEnIT is supported by the Louisiana Board of Regents. H.Z. and V.S. are undergraduate research assistants.
REFERENCES
1. A. K. Abbas, A. H. Lichtman and J. S. Pober, Cellular and Molecular Immunology. W.B. Saunders, Philadelphia, PA (2003).
2. D. Catty (Ed.)> Antibodies: A Practical Approach. IRL Press, Oxford (1996).
3. J. Fauchere and V. Pliska, Eur. J. Med, Chem, 18, 369 (1983).
4. T. P. Hopp and K. R. Woods, Proc. Natl. Acad. Sci. USA 78, 3824 (1981).
5. T. P. Hopp and K. R. Woods, Mol. Immunol. 20, 483 (1983).
6. P. Y. Chou and G. D. Fasman, Biochemistry 13, 211 (1974).
7. P, Y. Chou and G. D. Fasman, Adv. Enzymol. 47,45 (1978).
8. J. Kyte and R. F. Doolittle, J. Mol. Biol. 157, 105 (1982).
9. B. A. Jameson and H. Wolf, CABIOS 4, 181 (1999).
10. E. A. Emini, J. V. Hughes, D. S. Perlow and J. Boger, J. Virol. 55, 836 (1985).
11. J. Garnier, D. J. Osguthorpe and B. Robson, J. Mol. Biol. 120, 97 (1978).
12. R. H. Angeletti, J. Biomol. Tech. 10, 2 (1999).
13. R. K. Iler, J. Colloid Interface Sci. 21, 569 (1966).
14. I. Langmuir, US Patent No. 2,232,539, to General Electric Co. (1941).
15. G. Decher, Science 277, 1232 (1997).
16. Y. Lvov, in: Protein Architecture: Interfacial Molecular Assembly and Immobilization Biotech.nolugyFi. Lvov and H. MOhwald (Eds), p. 125. Marcel Dekker, New York, NY (2000).
17. M. Raposo and Ο. N. Oliveira Jr., Langmuir 18, 6866 (2002).
18. Y. Cheng and R. M. Corn, J. Phys. Chem. B, 103, 8726 (1999).
19. F. Boulmedais, P. Schwintd, C. Gergely, J.-C. Voegel and P. Schaaf, Langmuir 18, 4523 (2002).
20. Ph. Lavalie, C. Gergely, F. J. G. Cuisinier, G. Decher, P. Schaaf, J.-C. Voegel and C. Picart, Macromolecules 35, 4458 (2002).
21. D. T. Haynie, S. Balkundi, N. Palath, K. Chakravarthula and K. Dave, Langmuir 20, 4540 (2004).
22. B. Zheng, V. Surpuriya, K. Sabnis, H. Zhong and D. T. Haynie, Louisiana. Conference on Commercial Applications of Microsystems, Materials and Nanotechnologies, Oct. 21-22, Ruston, LA (2002).
23. H. Zhong, B. Zheng and D. T. Haynie, First CERT Biomedical Informatics Symposium, Nov. 5, Shreveport, LA (2002).
24. J. M. Krochta, in: Protein-Based Films and Coatings A. Gennadios (Ed.), p. I. CRC Press, Boca Raton, FL (2002).
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25. N. Pargaonkar, G. Sharma, K. Vistakula and D. T. Haynie, Louisiana Conference on Commercial Applications of Microsystems, Materials and Nanotechnologies, Ruston, LA (2002),
26. G. Decher and J. B. Schlenoff (Eds), Multilayer Thin Films. Wiley-VCH, Weinheim (2003).
27. K. Vistakula, G. Sharma, N. Pargoankar and D, T. Haynie, Louisiana Conference on Commercial Applications of Microsystems, Materials and Nanotechnologies, Ruston, LA (2002).
28. C. P. Stowell, J. Levin, B. D. Spiess and R. M. Winslow, Transfusion 41, 287 (2001).
29. A. Antipov, G. B. Sukhorukov, E. Donath and H. Mdhwald, J. Phys. Chem. B, 105, 2281 (2001).
30. M. Zasloff, Nature 415, 389 (2002).
31. J. KyngSs and J. Valjakka, Protein Eng. 11, 345 (1998).
32. C. Picart, J. Mutterer, L. Richert, Y. Luo, G. D. Prestwich, P. Schaaf, J.-C. Voegel and P. Lavalie, Proc. Natl. Acad. Sci. USA 99, 12531 (2002).
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IIIIIIIIIM
US 20050069950A1 (19) United States (12) Patent Application Publication (10) Pub. No.: US 2005/0069950 Al
Haynie (43) Pub. Date: Mar. 31,2005 (54) METHOD FOR DESIGNING POLYPEPTIDES FOR THE NANOFABRICATION OF THIN FILMS, COATINGS, AND MICROCAPSULES BY ELECTROSTATIC LAYER-BY-LAYER SELF ASSEMBLY (76) Inventor: Donald T. Haynie, Ruston, LA (US)
Correspondence Address:
Robert C. Tiicker
Jones, Walker, Waechter, Poitevent, Carrere & Denegre, L.L.P.
8555 United Plaza Boulevard, 5th Floor Baton Rouge, LA 70809 (US) (21) Appl. No.: 10/652,364 (22) Filed: Aug. 29, 2003
Publication Classification (51) bit. Cl.<sup>7</sup> ...........................GOIN 33/53 (52) U.S. Cl................................ 435/7.1 (57) ABSTRACT
A method for designing polypeptides for the nanofabrication of thin films, coatings, and microcapsules by ELBL for applications in biomedicine and other fields.
<img file="IL190885A_D0040.tif" />
US 2005/0069950 Al
Mar. 31, 2005
METHOD FOR DESIGNING POLYPEPTIDES FOR
THE NANOFABRICATION OF THIN FILMS,
COATINGS, AND MICROCAPSULES BY
ELECTROSTATIC LAYER-BY-LAYER SELF
ASSEMBLY
CROSS-REFERENCE TO RELATED APPLICATION
[0001] None.
STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT
[0002] None.
BACKGROUND OF THE INVENTION
[0003] A. Field of the Invention
[0004] The present invention relates to the fabrication of ultrathin multilayered films on suitable surfaces by electrostatic layer-by-layer self assembly (“ELBL”). More specifically, the present invention relates to a method for designing polypeptides for the nanofabrication of thin films, coatings, and microcapsules by ELBL for applications in biomedicine 1 and other fields.
[0005] B. Description of Related Art
[0006] ELBL is an established technique in which ultrathin films are assembled by alternating the adsorption of oppositely-charged polyelectrolytes. The processes based.oti, the reversal of the surface charge of the .«film after the deposition of each layer. FIG. 1 shows a schematic diagram of the general ELBL process: filmsof oppositely charged polyions (cationic polyions 10 and anionic polyibns 11) are assembled in successive layers on a negatively-charged planar surface 12; the surface charge is reversed after the deposition of each layer. This process is repeatedsiintiFa film of desired thickness is formed. The physical basis of association is electrostatics—gravitation and nuclear forces play effectively no role. Because of the generality and relative simplicity of the process, ELBL allows for the deposition of many different types of materials onto many different types of surface. There is, therefore, a vast number of possible useful combinations of materials and surfaces. For a general discussion of ELBL, including its history, see Yuri Lvov, “Electrostatic Layer-by-Layer Assembly of Proteins and Polyions” in Protein Architecture: Inlerfacial Molecular Assembly and Immobilization Biotechnology, Y. Lvov & H. Mohwald eds. (New York: Marcel Dekker, 1999), pp.125167, which is incorporated herein by reference in its entirety.
[0007] ELBL has recently become a focus area in the field of nanotechnology because it can be used to fabricate films substantially less than 1 micron in thickness. Moreover, ELBL permits exceptional control over the film fabrication process, enabling the use of nanoscale materials and permining nanoscale structural modifications. Because each layer has a thickness on the order of a few nanometers or less, depending on the type of material used and the specific adsorption process, multilayer assemblies of precisely repeatable thickness can be formed.
[0008] A number of synthetic polyelectrolytes have been employed in ELBL applications, including sodium poly(styrene sulfonate) (“PSS”), poly(allylamine hydrochloride) (“PAH”), poly(diallyldimcthylammonium chloride) (“PDDA”), poly(acrylamide-co-diallyldimethylammonium chloride), poly(ethyleneimine) (“PEI”), poly(acrylic acid) (“PAA”), poly(anetholesulfonic acid), poly(vinyl sulfate) (“PVS”), and poly(vinylsulfonic acid). Such materials, however, are not generally useful for biomedical applications because they are antigenic or toxic.
[0009] Proteins, being polymers with side chains having ionizable groups, can be used in ELBL for various applications, including biomedical ones. Examples of proteins that have been used in ELBL include cytochrome c, hen egg white lysozyme, immunoglobulin G, myoglobin, hemoglobin, and serum albumin (ibid.). There are, however, difficulties with using proteins for this purpose. These include limited control over multilayer structure (because the surface ofthc protein is highly irregular and proteins will not ordinarilysadsorb on a surface in a regular pattern), restrictions on pH due;,to the pH-dependence of protein solubility and structural stability, lack of biocompatibility when using exogenous proteins, and the cost of scaling up production if the gene has<sub>£</sub> not been cloned; unless the protein were identical'in a,readily available source, e.g. a cow, the protein would have to be obtained from the organism in which it was intended for use, making the cost of large-scale production ״ of thc protcin prohibitive.
[0010] By contrast polypeptides, which are generally x srhaller and less complex than proteins, constitute an excel. lent class of material for ELBL assembly, and polypeptide . film structures formed by ELBL will be useful in a broad ' range of applications. The present invention provides a method for designing polypeptides for the nanofabrication of thin films, coatings, and microcapsules by ELBL. Polypeptides designed using the method of the present invention should exhibit several useful properties, including, without limitation, completely determined primary structure, minimal secondary structure in aqueous solution, monodispersity, completely controlled net charge per unit length, ability to form cross-links on demand, ability to reverse cross-link formation, ability to form more organized thin films than is possible with proteins, and relatively inexpensive large-scale production cost (assuming gene design, synthesis, cloning, and host expression in E. coll or yeast, or peptide synthesis).
[0011] Polypeptides designed using the method of the present invention have been shown useful for ELBL of thin film structures with targeted or possible applications in biomedical technology, food technology, and environmental technology. Such polypeptides could be used, for example, to fabricate artificial red blood cells, drug delivery devices, and antimicrobial films.
BRIEF SUMMARY OF THE INVENTION
[0012] The present invention provides a novel method for identifying “sequence motifs” of a defined length and net charge at neutral pH in amino acid sequence information for use in ELBL, and recording a desired number of the motifs. The method comprises the steps of: (a) Obtaining an amino acid sequence for a peptide or a protein from a particular organism; (b) Locating a starter amino acid in the amino acid sequence; (c) Examining the starter amino acid and the following n amino acids to determine the number of charged amino acids having a polarity opposite the certain polarity;
US 2005/0069950 Al
Mar. 31, 2005 (d) If the number of the charged amino acids having a polarity opposite the certain polarity is one or more, continuing the method at step g; (e) Examining the starter amino acid and the following n amino acids to determine the number of charged amino acids having the certain polarity; (f) If the number of charged amino acids having the certain polarity is equal to or greater than x, recording the amino acid sequence motif consisting of the starter amino acid and the following n amino acids; (g) Locating another starter amino acid in the amino acid sequence; and (h) Repeating the method beginning at step c until the desired number of amino acid sequence motifs have been identified or all of the amino acids in the amino acid sequence have been used as the starter amino acid in step c; wherein x is greater than or equal to approximately one-half of n.
[0013] The present invention also provides a novel method for designing a polypeptide for use in ELBL, comprising the steps of: (a) Identifying and recording one or more amino acid sequence motifs having a net charge of a certain polarity using the steps mentioned in the preceding paragraph and (b) Joining a plurality of said recorded amino acid sequence motifs to form a polypeptide.
[0014] The present invention also provides a novel method for designing a polypeptide for use in ELBL comprising the following steps: (a) Designing de novo a plurality of amino acid sequence motifs, wherein said amino acid sequence motifs consist of n amino acids, at least x of which are: positively charged and none is negatively charged, or at least x of which arc negatively charged and none is positively charged, wherein x is greater than or equal to approximately one-half of n; and (b) Joining said plurality of said'amino acid sequence motifs. The amino acid sequence motifsican comprise the 20 usual amino acidsaor non-natural amino acids, and the amino acids can bev’either left-handed (L-amino acids) or right handed (D-amino acids).
[0015] The present invention also provides a thinsfilm, the film comprising a plurality of layers of polypeptides, the layers of polypeptides having alternating charges, wherein the polypeptides comprise al least one amino acid sequence motif consisting of n amino acids, at least x of which are positively charged and none is negatively charged, or at least x of which are negatively charged and none is positively charged, wherein x is greater than or equal to approximately one-half of n. The motifs in these polypeptides may be selected using either of the methods described above.
[0016] The present invention also provides a novel process for using cysteine or other sulfhydryl-containing amino acid types to “lock” and “unlock” the layers of polypeptide ELBL films. This process enables the films to remain stable at extremes of pH, giving greater control over the mechanical stability and diffusive properties of films nanofabricated from designed polypeptides and increasing their utility in a broad range of applications.
BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF TOE DRAWINGS
[0017] FIG. 1 is a schematic diagram of the general ELBL process.
[0018] FIG. 2 is a graph of the cumulative secondary structure propensities of the amino acid sequence motifs identified in human amino acid sequence information using the method of the present invention, compared with the distribution of structure propensities of 10<sup>5</sup> random amino acid sequences.
[0019] FIG. 3(a) shows adsorption data as monitored by the quartz crystal microbalance technique (“QCM”) for a combination of amino acid sequences designed according to the present invention.
[0020] FIG. 3(b) shows a comparison of adsorption data as monitored by QCM for different combinations of amino acid sequences designed according to the present invention.
[0021] FIG. 3(c) shows a graph of adsorbed mass in nanograms versus layer number for amino acid sequences designed and fabricated according to the present invention.
[0022] . FIG. 4(a) illustrates intra-layer disulfide bonds accordingHo the cysteine locking method of the present invention.
[0023]. «»FIG. 4(b) , illustrates inter-layer disulfide bonds according to the cysteine locking method of the present invention.
.[002’4] < FIG/4(c) illustrates the oxidation and reduction of disulfide bonds in microcapsules fabricated from polypeptides designed according to the method of the present invention.
[0025] FIG. 5 is a schematic of the selection process of the ' present invention used to identify in existing amino acid sequence information amino acid sequence motifs having suitable electrostatic properties for ELBL.
[0026] FIG. 6 shows the number of non-redundant sequence motifs identified in available human amino acid sequence data.
[0027] FIG. 7 shows the ELBL adsorption of poly-Lglutamate and poly-L-lysinc from an aqueous medium as a function of ionic strength.
[0028] FIG. 8 shows the adsorption of polypeptides designed according to the method of the present invention for experiments to probe the effect of disulfide bond formation.
[0029] FIG. 9 shows the percentage of material remaining during thin film disassembly at acidic pH as discussed with reference to FIG. 8.
[0030] FIG. 10 shows the percentage of material lost during the acidic pH disassembly step of an experiment involving de novo-designed polypeptides containing cysteine.
[0031] FIG. 11(a) illustrates the role of solution structure of peptides on film assembly, showing how the assembly behavior of poly-L-glutamate and poly-L-lysine depends on pH. QCM resonant frequency is plotted against adsorption layer. The average molecular mass of poly-L-glutamate was 84,600 Da, while that of poly-L-lysine was 84,000 Da. The numbers refer to pH values. E=Glu, K=Lys. The peptide concentration used for assembly was 2 mg/mL.
[0032] FIG. 11(h) illustrates the role of solution structure of peptides on film assembly, showing how the solution structure of poly-L-glutamate and poly-L-lysine depends on pH. Mean molar residue ellipticity is plotted as a function of pH. The peptide concentration was 0.05 mg/mL.
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[0045] As used herein, “non-natural amino acids” means amino acids other than the 20 naturally occurring ones.
[0046] The following three-letter abbreviations are used herein for the 20 usual amino acids:
[0033] FIG. 12 shows adsorption data for polyclcctrolytcs of different lengths, illustrating that long polyelectrolytes adsorb better than short ones.
DETAILED DESCRIPTION OF ׳THE INVENTION
[0034] A. Explanations of Terms
[0035] For convenience in the ensuing description, the following explanations of terms are adopted. However, these explanations are intended to be exemplary only. They are not intended to limit the terms as they are described or referred to throughout the specification. Rather, these explanations are meant to include any additional aspects and/or examples of the terms as described and claimed herein.
[0036] As used herein, “biocompatibility” means causing no adverse health effect upon ingestion, contact with the skin, or introduction to the bloodstream.
[0037] As used herein, “immune response” means the response of the human immune system to the presence of a substance in the bloodstream. An immune response can be characterized in a number of ways, for example, by an increase in the bloodstream of the number of antibodies that recognize a certain antigen. (Antibodies are proteins made , by the immune system, and an antigen is an entity that generates an immune response.) The human body fights^ infection and inhibits reinfection by increasing the number of antibodies in the bloodstream. The specific immune., response depends somewhat on the individual, though general patterns of response are the norm.
[0038] As used herein, “epitope” means thestruclureof.a־ protein that is recognized by an antibody. Ordinarily an epitope will be on the surface of a. protein. A “continuous epitope” is one that involves severaleamino acids in a row, not one that involves amino acid residues that happen to be in contact in a folded protein.
[0039] As used herein, “sequence motif’ and :“motif” mean an amino acid sequence of a given number of residues identified using the method of the current invention. In a preferred embodiment, the number of residues is 7.
[0040] As used herein, “amino acid sequence” and “sequence” mean any length of polypeptide chain that is at least two amino residues long.
[0041] As used herein, “residue” means an amino acid in a polymer; it is the residue of the amino acid monomer from which the polymer was formed. Polypeptide synthesis involves dehydration—a single water molecule is “lost” on addition of the amino acid to a polypeptide chain.
[0042] As used herein, “designed polypeptide” means a polypeptide designed using the method of the present invention, and the terms “peptide” and “polypeptide” are used interchangeably.
[0043] As used herein, “primary structure” means the linear sequence of amino acids in a polypeptide chain, and “secondary structure” means the more or less regular types of structure stabilized by non-covalent interactions, usually hydrogen bonds—examples include a-helix, β-sheet, and β-turn.
[0044] As used herein, “amino acid” is not limited to the 20 naturally occurring amino acids; the term also refers to D-amino acids, L-amino acids, and non-natural amino acids, as the context permits.
<td> Ala = alanine</td><td> Cys «. cysteine</td><td> Asp = aspartic acid</td>
<td> Glu = glutamic acid</td><td> Phe = phenylalanine</td><td> Gly = glycine</td>
<td> His ״ histidine</td><td> lie ״ isolcucinc</td><td> l.ys = lysine</td>
<td> Leu = leucine</td><td> Met ״ methionine</td><td> Asn = asparagine</td>
<td> Pro - proline</td><td> Gin - glutamine</td><td> Arg = arginine</td>
<td> Ser« serine</td><td> Thr - threonine</td><td> Vai » valine</td>
<td> Trp = tryptophan</td><td> Tyr = tyrosine</td><td></td>
[0047] B. Description of the Invention
[0048]' The present invention provides a method for designing polypeptides for the nanofabrication by ELBL of thin films,.coatings,and microcapsulcs for applications in biomedicine and otherficlds. The method involves 5 primary design concerns: (1) the electrostatic properties of the polypeptides;(2) the physical structure of the polypeptides; (3) the physical stability of the films formed from the polypeptides; (4) the biocompatibility of the polypeptides and films; and (5) the bioactivity of the polypeptides and films. The first design concern, electrostatics, is perhaps the most important because it is the basis of ELBL. Without suitable charge properties, a polypeptide will not be soluble in aqueous solution and cannot be used for the ELBL nanofabrication of films. We have devised a novel process for identifying in amino acid sequence information amino acid sequence motifs having electrostatic properties suitable for ELBL.
[0049] The secondary structure of the polypeptides used for ELBL is also important, because the physical properties of the film, including its stability, will depend on how the solution structure of the peptide translates into its structure in the film. FIG. 11 illustrates how the solution structure of certain polypeptides correlates with film assembly. Panel (a) shows how the assembly behavior of poly-L-glutamate and poly-L-lysine depends on pH. It is clear that the a-helix conformation correlates with a greater extent of deposited material than the β-sheet conformation. The precise molecular interpretation of this behavior remains to be elucidated. Panel (b) shows how the solution structure of these peptides depends on pH. At pH 4.2 poly-L-glutamate is largely a-hclical, as is poly-L-lysinc at pH 10.5. Both polypeptides are in a largely unstructured coil-like conformation at pH 7.3.
[0050] The remaining concerns relate to the applications of the polypeptide films. In practicing the invention, more or less weight will be placed on these other concerns depending on the design requirements of a particular application.
[0051] By using the selection process of the present invention to identify in amino acid sequence information amino acid sequence motifs having suitable charge characteristics, and using the other design concerns to select particular motifs, one can design polypeptides suitable for the ELBL fabrication of nano-organized films for applications in biomedicine and other fields. Alternatively, one can use the method of the present invention to design polypeptides de novo for use in ELBL. The approach to de novo design is
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[0059] Regarding biocompatibility (discussed further below), each identified sequence motif is long enough at 7 residues to constitute a continuous epitope (relevant to the possible immune response of an organism into which a designed peptide might be introduced), but not so long as to correspond substantially to residues both on the surface of a protein and in its interior; the charge requirements help to ensure that the sequence motif occurs on the surface of the folded protein; a charged residue cannot be formed in the core of a folded protein. By contrast, a very short motif could appear to the body to be a random sequence, or one not specifically “self,” and therefore elicit an immune response. Although the ideal length of a peptide for generating antibodies is a point of some dispute, most peptide antigens range in length from 12 to 16 residues. Peptides that are 9 residues or shorter can be effective antigens; peptides longer than 12 ¾16 amino acids may contain multiple epitopes (Angclctti/R. H. (1999) Design of Useful Peptide Antigens, J. Biomol. Tech. 10:2-10, which is hereby incorporated by reference in its entirety). Thus, to minimize antigenicity one would prefer apeptideshorter than 12 and, better yet, shorter than 9 residues; »
[0060] The preferred motifs should not be too long for another reason: to minimize secondary structure formation. Secondary structure decreases control of the physical structure of the polypeptides (see below) and the films made from them.
[0061] Furlhertnore, the maximum number of non-redundant motifs is found when the number of residues in each motif is 7. FIG. 6 shows the number of non-redundant sequence motifs in available human amino acid sequence information. The greatest number of positive motifs is for a 5-residue length, while the greatest number of negative motifs is for a 7-residue length. The greatest number of positive and negative motifs is about the same for 5 and 7. Thus, a motif length of 7 residues would appear to maximize the number of non-redundant motifs.
[0062] For all of the above reasons, 7 residues is the preferred length of motif to optimize polypeptide design for ELBL. Nevertheless, it is possible that in some cases either slightly shorter or slightly longer motifs will work equally as well. For example, motifs 5 or 6 residues long may be employed, and motifs on the order of 8 to 15 residues in length could also be useful.
[0063] b. Number of Charged Residues
[0064] Second, it is preferred that at least 4 positivelycharged (basic) amino acids (Arg, His, or Lys) or at least 4 negatively-charged (acidic) amino acids (Glu or Asp) are present in each 7-rcsiduc motif at neutral pH. Combinations of positive and negative charges are disfavored in an effort to ensure a sufficiently high charge density at neutral pH. It is possible, however, that a motif containing both positive and negative amino acids could be useful for ELBL. For example, a slightly longer motif, say of 9 residues, could have 6 positively charged amino acids and 1 negatively charged amino acid. It is the balance of charge that is important—the overall peptide must be either sufficiently positively charged or sufficiently negatively charged at ncutral pH. Preferred embodiments of the motifs, however, will contain only Glu or Asp or only Arg, His, or Lys as the charged amino acids (although other non-charged amino essentially the same as identifying motifs in existing amino acid sequence information, except that each residue in an amino acid sequence motif is selected by the practitioner rather than an entire motif being identified in the genomic or proteomic information of a specific organism. It must be emphasized that the fundamental polypeptide design principles adduced in the present invention are independent of whether the amino acids involved are the 20 naturallyoccurring ones, non-natural amino acids, or some novel combination of these, in the case of de novo polypeptide design. Further, both D-amino acids and L-amino acids could be used.
[0052] The design concerns of the present invention are discussed in more detail below.
[0053] 1. Electrostatics
[0054] We have devised a novel process for identifying in amino acid sequence information amino acid sequence motifs having electrostatic properties suitable for ELBL. Using this process, we have identified 88,315 non-redundant amino acid sequence motifs in human proteome data—the translation of the portion of the genome that encodes all known proteins in the human body. This information is publicly available at the National Center for Biotechnology ״״' Information’s (“NCBI”) Web site: <http://www.ncbi.nlm.nih.gov>, among other places. Such information is constantly being updated as the human genome is further analyzed. As [ <sub>s </sub>the amount of such information increases, the number of amino acid sequence motifs that could be identified in . human sequence information by the selection process'd{ the present invention as having suitable electrostatic properties for ELBL will also increase. The same is true for. any organism. Accepted biochemical anckphysic'sipnnciples, as well as the experimental results described below, indicate that the identified sequence motifs wilbbe^.useful for the design of polypeptides for the nanofabric’atioti of ELBL structures.
[0055] The key selection criterion is the average charge per unit length at neutral pH (pH 7, close to the pH of human blood). In addition, there are several structural preferences. First, it is preferred that each amino acid sequence motif consist of only ר residues.
[0056] a. Total Number of Residues in the Motif
[0057] The motif length of 7 was chosen in an effort to optimize biocompatibility, physical structure, and the number of non-redundant sequence motifs in available amino acid sequence data.
[0058] As discussed below, it is preferred that at least half of the amino acid residues in each sequence motif be charged. Moreover, it is preferred that all of the charged residues in each motif be of the same charge. These requirements ensure that each motif will be sufficiently soluble in aqueous solvent and have sufficient charge at neutral pH to be useful for ELBL. Because only a relatively small percentage of amino acid types are charged, as the length of a given amino acid sequence increases, the odds decrease that the sequence will have a sufficient percentage of appropriatcly charged amino acids for ELBL. 4 charged amino acids is the preferred minimum for a motif size of 7, because fewer than 4 charges yields substantially decreased peptide solubility and decreased control over ELBL.
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[0065] FIG. 5 is a flow chart showing the steps involved in the selection process for identifying amino acid sequences having suitable electrostatic properties. It is assumed that only the 20 usual amino acids are involved. If searching for negatively-charged motifs, the process begins by locating an amino acid in the sequence data. This amino acid will be called the “starter amino acid” because it is the starting point for the analysis of the surrounding amino acids (i.e., it will begin the motif). Next, the starter amino acid and the following 6 residues are examined for occurrences of Arg, His, or Lys. If one or more Arg, His, or Lys is located in these 7 amino acids, the process is begun anew at another starter amino acid. If no Arg, His, or Lys is found, the 7 amino acids are examined to determine the number of occurrences of Glu and/or Asp. If there are at least 4 occurrences of Glu and/or Asp in the 7 residues, the sequence motif is cataloged. The selection process is essentially the same for positively charged amino acids, except that Glu and Asp are replaced by Arg, His, and Lys, and Arg, His, and Lys are replaced by Glu and Asp, respectively. Obviously, one could also begin λ the method at the beginning of the amino acid sequence '.’ (amino terminus) and proceed to the end (carboxyl tcrmi-;. nus), or, alternatively, one could begin at a random point and work through all of the amino acids in the sequence,’randomly or systematically in cither direction. Moreover, י® one could use the method to identify motifs in sequence information containing non-natural amino -acids״ .for f example, if codes were used for each non-natural amino acid type. In such a case, one would search for non-natural'acidic or basic amino acids instead of Gltittand Asp; :and Arg, Lys, and His, respectively.
[0066] The remaining design concerns, namely, physical structure, physical stability, biocompatibility, and biofunctionality, deal primarily with the particular application for which the designed polypeptides will be used. As noted above, more or less weight will be placed on these concerns during the design process, depending on the desired peptide properties for a particular application.
[0067] 2. Physical Structure
[0068] A design concern regarding the amino acid sequence motifs is their propensity to form secondary struclures, notably a-helix or β-sheet. We have sought in several ways to control, notably minimize, secondary structure formation of designed polypeptides in an aqueous medium in order to maximize control over thin film layer formation. First, it is preferred that the sequence motifs be relatively short, because long motifs arc more likely to adopt a stable three-dimensional structure in solution. Second, we place a glycine residue between each motif in preferred embodiments of the polypeptide designs. Glycine has a very low a-helix propensity and a very low β-sheet propensity, making it energetically very unfavorable for a glycine and its neighboring amino acids to form regular secondary structure in aqueous solution. Proline has similar properties in some respects and could be used as an alternative to glycine to join motifs. Third, we have sought to minimize the a-hclix and β-sheet propensity of the designed polypeptides themselves by focusing on motifs for which the summed a-helix propensity is less than 7.5 and the summed β-sheet propensity is less than 8. (“Summed” propensity means the sum of the a-helix or β-sheet propensities of all amino acids in a motif.) It is possible, however, that amino acid sequences having a somewhat higher summed a-helix propensity and/or summed β-sheet propensity would be suitable for ELBL under some circumstances, as the Gly (or Pro) residues between motifs will play a key role in inhibiting stable secondary structure formation in the designed polypeptide. In fact, it may be desirable in certain applications for the propensity of a polypeptide to form secondary structure to be relatively high, as a specific design feature of thin film fabrication; the necessary electrostatic charge requirements for ELBL must still be met, as discussed above.
[0069] In order to be able to select amino acid sequences with desired secondary structure propensities, we first calculatedthe secondary structure propensities for all 20 amino acidS'Usingjthe method of Chou and Fasman (see P. Chou and G. Fesm&nlliochemistry 13:211 (1974), which is incorporated-by reference herein in its entirety) using structural information'from more than 1,800 high-resolution X-ray crystallographic structures (1,334 containing a-helices and l,221׳«conta1ning β-strands). Structures were selected from the Protein Data Bank (a publicly-accessible repository of protein structures) based on: (a) method of structure deterruination (X-ray diffraction); (b) resolution (better than 2.0 ,0)—“resolution” in this context refers to the minimum size of a structure one can resolve, as in the Rayleigh criterion; and (c) structural diversity (less than 50% sequence identity between the protein crystallographic structures used to computc the helix and sheet propensities of the various amino acids). The rationale was to choose high resolution structures determined by the most reliable methodology and not to bias the propensity calculation by having similar structures. Next, for comparison 100,000 non-redundanl random sequences were produced using a random number generator in a personal computer. We then calculated the secondary structure propensities for the 88,315 amino acid sequences identified using the selection process described in part VII(B)(1) above (59,385 non-redundant basic sequence motifs and 28,930 non-redundant acidic sequence motifs). The propensities for the random sequences were then compared to the propensities of the selected sequences. FIG. 2 shows the distribution of secondary structure formation propensities in these sequence motifs. The rectangle in FIG. 2 highlights the sequence motifs we have identified as least likely to form secondary structure on the basis of secondary structure propensities.
[0070] 3. Physical Stability
[0071] Another design concern is control of the stability of the polypeptide ELBL films. Ionic bonds, hydrogen bonds, van dcr Waals interactions, and hydrophobic interactions provide some, albeit relatively limited, stability to ELBL films. By contrast, covalent disulfide bonds could provide exceptional structural strength. We have devised a novel process for using cysteine (or some other type of sulfhydrylcontaining amino acid) to “lock” and “unlock” adjacent layers of polypeptide ELBL film. This process enables a polypeptide nanofabricated film to remain stable at extremes of pH, giving greater control over its mechanical stability and diffusive properties (for discussions of porosity of multilayer films made of non-polypeptide polyelectrolytes, see Caruso, F., Niikura, K., Furlong, N. and Okahata (1997) Langmuir 13:3427 and Caruso, F., Furlong, N., Ariga, K.,
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Ichinosc, I., and Kunitake, 1’. (1998) Langmuir 14:4559, both of which arc incorporated herein by reference in their entireties). Also, the incorporation of cysteine (or some other type of sulfhydryl-containitig amino acid) in a sequence motif of a designed polypeptide enables the use of relatively short peptides in thin film fabrication, by virtue of intermolecular disulfide bond formation. Without cysteine, such peptides would not generally yield sufficiently stable films (see FIG. 12, discussed below). Thus, our novel use of cysteine will obviate the need to produce expensive long versions of the designed polypeptides in a substantial percentage of possible applications. This will be particularly advantageous in situations where the thin film is to be fabricated over material to be encapsulated, for example a small crystal of a drug, a small spherical hemoglobin crystal, or a solution containing hemoglobin.
[0072] For applications in which the physical stability of the films is important, amino acid sequence motifs containing cysteine (or some other type of sulffiydryl-containing amino acid) may be selected from the library of motifs identified using the methods discussed above, or designed de novo using the principles described above. Polypeptides can then be designed and fabricated based on the selected or designed amino acid sequence motifs. Once the polypeptides have been synthesized chemically or produced in a host, organism, ELBL assembly of cysteine-contaimng peptides is done in the presence of a reducing agent, to prevent premature disulfide bond formation. Following assembly) the reducing agent is removed and an oxidizing agent is:added. In the presence of the oxidizing agent disulfide bondsform between cysteine residues, thereby “locking” together the polypeptide layers that contain them. Ιϊ
[0073] This “locking” method may be further illustrated using the following specific example of microcapsule fabrication. First, designed polypeptides containing cysteine are used to form multilayers by ELBL on a suitably charged spherical surface, normally in aqueous solution at neutral pH and in the presence of dilhiothreitol (“DTT”), a reducing agent. Next, DTT is removed by filtration, diffusion, or some other similar method known in the art, causing cystine to form from pairs of cysteine side chains and thereby stabilizing the film. If the peptide multilayers are constructed on a core particle containing the materials one wishes to encapsulate, for instance a crystalline material, the fabrication process is complete and the core particle can thereafter be made to dissolve in the encapsulated environment, for example by a change of pH. If, however, the multilayers are constructed on a “dummy” core particle, the core must be removed. In the case of melamine formaldehyde particles (“MF”), for example, the core is ordinarily dissolved by decreasing the pH”—dissolution is acid-catalyzed. Following dissolution of the core, the pH of solution is adjusted to 4, where partial charge on the peptide polyanions makes the microcapsules semi-permeable (compare Lvov et al. (2001) Nano Letters 1:125, which is hereby incorporated herein in its entirely). Next, 10 mM DTI' is added to the microcapsule solution to reduce cystine to cysteine. The microcapsules may then be “loaded” by transferring them to a concentrated solution of the material to be encapsulated, for example a protein (ibid.). The protein enters the microcapsulcs by moving down its concentration gradient. The encapsulated protein is “locked in” by removal of reductant and addition of oxidant, thereby promoting the reformation of disulfide bonds.
[0074] Aschctnatic of the cysteine “locking” and “unlocking” method of the present invention is shown in FIG. 4. Cysteine can form both intra- and inter-molecular disulfide bonds. Further, disulfide bonds can be formed between molecules in the same layer or adjacent layers, depending on the location of cysteine-containing peptides in the film. Referring to FIG. 4(a), basic polypeptides 2 are linked by disulfide bonds 3 in all layers in which the basic peptides contain cysteine. The acidic peptides of the intervening layer (represented in the figure by a translucent layer 4) do not contain cysteine. However, alternating layers continue to attract each other electrostatically, if the acidic and basic side chains are charged at the pH of the surrounding environment. Referring to FIG. 4(/>), disulfide bonds are shown between layers. Such structures will form when both the acidic and basic polypeptides (i.e., alternating polypeptide layers) ,used for ELBL contain cysteine and the procedure used has been suitable for disulfide bond formation. Referring to FIG. 4(c).;.reduction and oxidation reactions are used to regulateUhe release of encapsulated compounds 5 by breakmg and forming disulfide bonds 3, respectively, and therebyregulating the diffusion of particles through the capsule'wall.
s' [0075] The cysteine “locking” and “unlocking” is a novel s way ofregulating the structural integrity and permeability of ELBL films. It is known in the art that glutaraldehyde can be . ’ used to cross-link proteins, and this chemical could therefore be used to stabilize polypeptide films. Glutaraldehyde cross' linking, however, is irreversible. In contrast, the cysteine .־ “locking” and “unlocking” method of the present invention is reversible and, therefore, offers better control over stateture formation and, importantly, use of the films and capsules that can be fabricated using the present invention. Blood is an oxidizing environment. Thus, in certain biomedical applications, for example artificial red blood cells or drug delivery systems fabricated from designed polypeptides, exposing Cys-crosslinked polypeptide film to the blood or some other oxidizing environment after the formation of disulfide bonds is not expected to cause those bonds to be broken. Finally, it should also be noted that applicalions involving non-natural amino acids would replace Cys with some other sulfhydryl-containing amino acid type. For example, a sulfhydryl could be added to β-amino acids such as D,L־p־amino־P-cylohexyl propionic acid; D,L-3-aminobutanoic acid; or 5-(tnethyllhio)-3-aminopentanoic acid (see http://www.synthatex.com).
[0076] 4. Biocompatibility
[0077] Biocompatibility is a major design concern in biomedical applications. In such applications, the practitioner of the present invention will aim to identify genomic or proteomic information that will yield “immune inert” polypeptides, particularly if the fabricated or coated object will make contact with circulating blood. For purposes of the present invention, it is preferred that the selection process discussed in Part VH(B)(1) above be used to analyze the amino acid sequences of blood proteins. This will maximize the odds of minimizing the immune response of an organism.
[0078] Computer algorithms exist for predicting the antigenicity of an amino acid sequence. Such methods, however, are known in the art to be semi-reliable at best. In the present invention, the sequence motifs identified using the selection
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Mar. 31, 2005 method discussed above in Part VII(B)(1) arc highly polar. The motifs must, therefore, occur on the surface of the native state of the proteins of which they are part of the sequence. The “surface” is that part of a folded protein that is in contact with the solvent or inaccessible to the solvent solely because of the granular nature of water. The “interior” is that part of a folded protein that is inaccessible to solvent for any other reason. A folded globular soluble protein is like an organic crystal, the interior being as densely packed as in a crystal lattice and the exterior being in contact with the solvent, water. Because of their charge properties, the polypeptide sequence motifs identified using the method of the present invention must occur mostly, if not exclusively, on the surface of a protein. Thus, all of the sequence motifs identified in human blood proteins using the selection process of the current invention are effectively always in contact with the immune system while the protein is in the blood. This holds for all conformations of the protein that might become populated in the bloodstream, including denatured states, because it is highly energetically unfavorable to transfer a charge from an aqueous medium to one of low dielectric (as occurs in a protein interior). Accepted biochemical principles indicate, therefore, that the polypeptides designed from blood proteins using the method of the present invention will cither not illicit an immune response or will elicit a minimal immune response. For the ,same* reasons, polypeptides designed using the method of the' present invention should be biocompatiblc. /Ml sequence motifs identified from genomic data using the selection . process of the current invention, not only thosejin,blood' proteins, should be biocompatiblc, though the extent of immune response or any other type of biological response may well depend on specific details ;of . a sequence motif. (Because the polypeptide sequences on which the motifs are based actually occur in the organism for which, the film as been fabricated, this approach will, at least in !principle, work equally well for any type of organism. For instance, the approach may be of significant value to veterinary science.) Both immune response and biocompatibility are important regarding the use of the designed peptides in biomedical applications, including, without limitation, the manufacture of artificial red blood cells, drug delivery systems, or polypeptides for fabrication of biocompatible films to coat implants for short-term or long-term introduction into an organism.
[0079] 5. Bioactivity
[0080] In some applications of polypeptide thin films, coatings, or microcapsules, it may be desirable to modify the design of the polypeptides to include a functional domain for use in some layer of the structure, often the outermost. A functional domain in this context is an independently thermostable region of a protein that has specific biofunctionality (e.g. binding phosphotyrosine). It is well known in the art that such biofunctionality may be integrated with other functionalities in a multi-domain protein, as for example in the protein tensin, which encompasses a phosphotyrosine binding domain and a protein tyrosine phosphatase domain. The inclusion of such a domain in a designed polypeptide could function in a number of ways, including without limitation specific ligand binding, targeting in vivo, biosensing, or biocatalysis.
[0081] C. Uses for Polypeptides Designed Using the
Method of the Present Invention
[0082] As noted above, polypeptides of suitable design are excellent materials for ELBL, and polypeptide film structures formed using ELBL will be useful in a large number of different types of applications. Polypeptides designed using the method of the present invention have been shown to be useful for ELBL of film structures for possible applications in biomedical technology, food technology, and environmental technology. For example, such polypeptides could be used to fabricate artificial red blood cells.
[0083] 1. Artificial Red Blood Cells
[0084] A number of different approaches have been taken to red blood cell substitute development. One approach involves the use of perfluorocarbons. Perfluorocarbon cmulsions contain.synthetic fluorinated hydrocarbons capable of binding oxygen and delivering it to tissues. This approach however,! increases reticulo-endothelial cell blockage. The perfluorocarbons can become trapped in the reticulo-endothelial system, which may result in adverse consequences.
[0085] '־ Another approach focuses on antigen camouflag״ing, which' involves coating red blood cells with a biocompatible.polymer called polyethylene glycol (PEG). The PEG . molecules form permanent covalent bonds on the surface of the. cell. The coating effectively hides the antigenic molH ecules on the surface of the red blood cells, so that the blood <sup>1</sup>'<sup>,</sup>recipient’s antibodies do not recognize the cells as foreign.
For example, the immune system of a normal person who has type A blood will naturally have antibodies that recognize antigens on the surface of type B red blood cells, leading to cell destruction. The attachment of PEG to the surface of a type B red blood cell “camouflages” the surface of the cell, so that its surface antigens can no longer be recognized by the immune system and the antigenicallyforeign red blood cells will not be destroyed as quickly (see Pargaonkar, N. A., G. Sharma, and K. K. Vistakula. (2001) “Artificial Blood: Current Research Report,” which is hereby incorporated by reference in its entirety).
[0086] A number of diseases, including thalassemia, that require repeated blood transfusions are often complicated by the development of antibodies to “minor” red cell antigens. This “allosensitization” can render these patients almost impossible to transfuse, rendering the situation life-threatening. In in vitro testing, the PEG-modified red cells appear not to trigger allosensitization and may also be useful in clinical situations where allosensitization has already occurred (see Scott, M. D. et al. (1997) “Chemical camouflage of antigenic determinants: Stealth erythrocytes,”Proc. Natl. Acad. Sci. USA. 94 (14): 7566-7571, which is hereby incorporated by reference in its entirety).
[0087] Other approaches involve purified hemoglobin. Unmodified cell-free hemoglobin has known limitations. These include oxygen affinity that is too high for effective tissue oxygenation, a half-life within the intravascular space that is too short to be clinically useful, and a tendency to undergo dissociation into dimers with resultant renal tubular damage and toxicity. Because of these limitations, hemoglobin used to make a cell-free red blood cell substitute must be modified. A number of modification techniques have been developed. Hemoglobin can be cross-linked (a covalent bond between two molecules is made by chemical modifi
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Mar. 31, 2005 cation) and polymerized using reagents such as glutaraldchyde. Such modifications result in a product that has a higher P<sub>50</sub> (partial pressure of oxygen at which 50% of all oxygenbinding sites are occupied) than that of normal hemoglobin, and an increase in the plasma half-life of up to 30 hours. The source of the hemoglobin for this purpose can be human (outdated donated blood), bovine, or human recombinant. The solution of modified hemoglobin is prepared from highly purified hemoglobin and taken through various biochemical processes, to eliminate phospholipids, endotoxins, and viral contaminants (see Nester, T. and Simpson, M (2000) “Transfusion medicine update,”Blood Substitutes, which is hereby incorporated by reference in its entirety). Biopure Corporation (Cambridge, Mass.) has been using modified hemoglobin for their product, Hemopure.
[0088] The main potential adverse effect of modified hemoglobin solutions is an increase in systemic and pulmonary vascular resistance that may lead to a decrease in cardiac index. Decreases in the cardiac index may impair optimum oxygen delivery and outweigh the advantage of an oxygen-carrying solution (see Kasper S. M. et al. (1998) “The effects of increased doses of bovine hemoglobin on hemodynamics and oxygen transport in patients undergoing preoperative hemodilution for elective abdominal aortic surgery,”A aesr/1. Analg. 87: 284-91, which is hereby incurporated by reference in its entirety). One study has examined the utility of these solutions in the acute rcsuscitatiomphasei of unstable trauma patients. Design of the study, howcvei. was poor, and any role of the solutions in influencing h ultimate patient outcome was unclear (see Koenigsberg D. et al. (1999) “The efficacy trial of diaspirin cross-linked hern0globin in the treatment of severe traumatic hemorrhagic shock,”Acad. Emerg. Med. G: 379/80, which is hereby incorporated by reference in its entirety).
[0089] Many of the problems of cell-freeshemoglobin can be overcome by encapsulating it with an artificiaLmembrane. Liposomes are being used to encapsulate hemoglobin for use as a blood substitute. The approach is technically challenging because not only must the hemoglobin be prepared, it must be encapsulated in relatively high concentration and yield. The final products must be sterile and the liposomes must be relatively uniform in size.
[0090] Encapsulated hemoglobin has several advantages over cell-free hemoglobin, firstly, the artificial cell membrane protects hemoglobin from degradative and oxidative forces in the plasma. Secondly, the membrane protects the vascular endothelium from toxic effects of hemoglobin. These relate to heme loss, the production O<sub>2</sub> free radicals and vasoconstrictor effects of NO binding. Thirdly, encapsulation greatly increases the circulating persistence of the hemoglobin. Moreover, encapsulated hemoglobin can be freeze-dried for convenient storage.
[0091] Liposomal encapsulation involves phospholipids, as in cell membranes. One major problem associated with liposomal encapsulation, however, is that it is very difficult to regulate the average size and distribution of liposomes. Another is that unlike red blood cells, liposomes are often not very stable, as they ordinarily lack an organized cytoskclcton. Yet another problem is that liposomes often consist of multiple layers of phospholipid. (Arecent review of blood substitute development is presented in Stowell et al. (2001) Progress in the development of RBC substitutes, Transfu sion 41:287-299, which is hereby incorporated by reference in its entirety. See also Chang, T. 1998 “Modified hemoglobin-based blood substitutes: cross linked, recombinant and encapsulated hemoglobin,”Artificial Cell 74 Suppl 2:23341, which is hereby incorporated by reference in its entirety.)
[0092] Red blood cell substitutes employing polypeptides designed using the method of the present invention should offer several advantages over approaches to the development of red blood cell substitutes known in the art, including, without limitation, superior oxygen and carbon dioxide binding functionality, lower production cost (large-scale and therefore low-cost production is possible because bacteria can be used to mass-produce the peptides and because peptide ELBL can be automated), the possibility of using suitable preparations of hemoglobin as a template for ELBL, polypeptide biodegradability, the immune “inertness” of designed'pplypeptides based on blood protein structure, and the structuralsstability exhibited by designed polypeptide films, which exceeds that of liposomes. Polypeptide ELBL assembly yields semi-porous films, minimizing the amount of material required forfabricating a means of encapsulation andienablingiglucose, oxygen, carbon dioxide, and various metabolites to diffuse as freely through the films as a lipid bilayer. In contrast, other polymers potentially suitable for this *purpose have undesirable side effects—for example, polylactide degrades into lactic acid, the substance that causes muscle cramps, and poly (styrene sulfonate) is not > biocompatible.
<sup>4</sup>[0093] Microcapsules could be formed of designed polypeptides to encapsulate hemoglobin to serve as a red blood cell substitute. Hemoglobin polypeptide microcapsules could also be engineered to incorporate enzymes, including superoxide dismutase, catalase, and methemoglobin reductase, which arc ordinarily important for red blood cell function. Moreover, the nanofabricated microcapsules can predictably be dehydrated, suggesting that artificial red blood cells made as described herein could be dehydrated, without loss of function, particularly because hemoglobin can be lyophilized (i.e., freeze-dried) and reconstituted without loss of function, and polyion films are stable to dehydration. This will be important for long-term storage, transport of blood substitutes, battlefield applications (particularly in remote locations), and space exploration.
[0094] Polypeptides designed using the method of the present invention could also be used for drug delivery.
[0095] 2. Drug Delivery
[0096] Micron-sized “cores” of a suitable therapeutic material in “crystalline” form can be encapsulated by designed polypeptides, and the resulting microcapsules could be used for drug delivery. The core must be insoluble under some conditions, for instance high pH or low ternperature, and soluble under the conditions where controlled release will occur. The surface charge on the crystals can be determined by ζ-potenlial measurements (used to determine the charge in electrostatic units on colloidal particles in a liquid medium). The rate at which microcapsule contents are released from the interior of the microcapsule to the surrounding environment will depend on a number of factors, including the thickness of the encapsulating shell, the polypeptides used in the shell, the presence of disulfide bonds, the extent of cross-linking of peptides, temperature, ionic strength, and the method used to assemble the pepUS 2005/0069950 Al
Mar. 31, 2005 tides. Generally, the thicker the capsule, the longer the release time—the principle resembles that of gel filtration chromatography.
[0097] Some work has been done on sustained release from ELBL microcapsules (see Antipov, A., Sukhorukov, G. B., Donath, E., and Mohwald, H. (2001)./. Phys. Chem. B, 105:2281-2284 and Freemantle, M. (2002) Polyelectrolyte multilayers, Chem. Eng. News, 80: 44-48, both of which are incorporated herein by reference in their entireties). Polyelectrolytes that have been used are PSS, PAH, PAA, PVS, PEI, and PDDA.
[0098] Polypeptides designed using the method of the present invention should offer a number of advantages in the context of drug delivery, including without limitation control over the physical, chemical, and biological characteristics of the microcapsule; the ability to make capsules with a diameter of less than 1 mm, making the capsules suitable for injection; low likelihood of eliciting an immune response; generally high biocompatibility of capsules; control over the diffusive properties of the microcapsules by varying the thickness of the layers and using cysteine, as discussed below; the ability to target specific locations by modification of the microcapsule surface using the highly reactive sulf- ,. hydryl groups in cysteine (as is well known in the art, free 'י sulfhydryl groups, free amino groups, and free carboxyl« groups are sites to which molecules for specific targeting could be attached), or by incorporation of a specific/func-<sup>s!</sup>“ tional domain in the design of the polypeptide; !and the ability of microstructures to be taken up by cells usingjeitber endocytosis or pinocytosis.
[0099] Polypeptides designed using the,JmethodW||the present invention could also be used for antimicrobial coatings. , :.:¾
[0100] 3. Antimicrobial Coatings
[0101] The method of the present invention could be used to manufacture films encompassing antimicrobial'peptides. For example, one suitable sequence might be Histatin 5, which occurs in humans:
food covers, wraps, and separation layers; food casings, pouches, bags, and labels; food coatings; food ingredient microcapsules; drug coatings, capsules, and microcapsules; disposable food service items (plates, cups, cutlery); trash bags; water-soluble bags for fertilizer and pesticides; microcapsules for fertilizer and pesticides; agricultural mulches; paper coatings; loose-fill packaging; disposable medical products (e.g. gloves and gowns); and disposable diapers.
[0106] D, Fabrication
[0107] Once amino acid sequence motifs have been selected from those identified using the method discussed in Part VI 1(B)(1) above or designed de novo, the designed polypeptide is synthesized using methods well known in the art, such as solid phase synthesis and F-moc chemistry or heterologous expression following gene cloning and transformation,<sup>,</sup>:Designed polypeptides may be synthesized by a peptide synthesis company, for example SynPep Corp. (Dublin, Calif.), produced in the laboratory using a peptide synthesizer;sor produced by recombinant methods.
[0108] In one embodiment, a designed polypeptide consists.of individual amino acid sequence motifs joined in . tandem. The same motif may be repeated, or different motifs may be joined in designing a polypeptide for ELBL. Moreover, functional domains may be included, as discussed above. Other amino acids than glycine could be used to link the sequence motifs, and amino acids other than the 20 usual *ones could be included in the motifs themselves, depending ™ on the properties desired of the polypeptide. Other properties could likewise be specified by design requirements, using methods known in the art. For example, proline could be included for turn formation, glycine for chain flexibility, and histidine for pH-sensitive charge properties near neutral pH. “Hydrophobic” amino acids could also be included— hydrophobic residue content could play a role in assembly behavior and contribute to layer stability in a way rcsembling the hydrophobic stabilization of globular proteins.
[0109] It is preferred that fabricated polypeptides be at least 15 amino acids long, although it is more preferred that
Asp Ser His Ala Lys Arg His His Gly Tyr Lys Arg Lys His Glu (SEQ ID NO: 8)
Lys His His Ser His Arg Gly Tyr
[0102] The preponderance of positive charge at slightly basic pH makes this sequence quite suitable for ELBL. It could be appended to a peptide designed using the method of the present invention, resulting in an antimicrobial peptide suitable for use in ELBL. This peptide could be used as an anti-biofouling coating. For instance, the peptide could be used to form a coating on devices used for implantation.
[0103] There are also a number of other areas in which polypeptides designed using the method of the present invention could be useful.
[0104] 4. Other Uses
[0105] Other possible uses for peptides designed using the method of the present invention include without limitation the fabricated polypeptides be at least 32 amino acids long. The reason for this is that the entropy loss per molecule is so thermodynamically unfavorable for short polymers that adsorption to an oppositely-charged surface is inhibited, even if the polypeptide has a charge per unit length of 1; long polyelectrolytes adsorb better than short ones. <sup>,</sup>This is illustrated in FIG. 12. The average molecule masses of the peptides utilized for the length-dependence studies were 1,500-3,000 Da (poly-L-glutamate, “small”), 3,800 Da (poly-L-lysine, “small”), 17,000 Da (poly-L-glutamate, “medium”), 48,100 Da (poly-L-lysinc, “medium”), 50,300 Da (poly-L-glutamate, “large”), and 222,400 Da (poly-Llysine, “large”). The data shown in FIG. 12 clearly indicate that ELBL depends on length of peptide. Inclusion of Cys enables the use of relatively small peptides for ELBL,
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Mar. 31, 2005 because the sulfhydryl group can be used to form disulfide crosslinks between polypeptides.
[0110] E. Experiments
1. Example 1
Design of Polypeptides Based on Human Blood Protein Sequences and their Use in Polypeptide Film Fabrication
[0111] For this work, amino acid sequences were selected using the process described in Part VII(B)(1) above to identify sequence motifs io the primary structure of human blood proteins: Complement C3 (gi|68766) was the source of the anionic sequence motifs, and lactotransferrin (gi|4505043) the source of the cationic sequence motifs. As discussed above, blood protein sequences were used to minimize the immune response of patients into whom devices involving the polypeptides might be introduced (including, e.g. artificial red blood cells). In principle, this approach should be applicable for any organism having an immune system; it is not limited to humans. Polypeptides were synthesized by SynPep Corp. (Dublin, Calif.). The polypeptide sequences were:
[0113] The polypeptides were named SN1 (SEQ ID NO: 2), SP2 (SEQ ID NO: 1), LN3 (SEQ ID NO: 4), and LP4 (SEQ ID NO 3), respectively, meaning short negative, short positive, long negative, and long positive. These sequences are quite different from polylysine (commonly used in the art as a polycation) and polyglutamate (commonly used in the art as a polyanion) which, though available commercially and inexpensive, have a high a-helix propensity under conditions of mild pH and, crucially, arc immunoreactive. The calculated charge per unit length on the designed peptides at neutral pH is 0.5 electrostatic units for SP and LP and 0.6 electrostatic units for SN and LN. The positive peptides are somewhat more hydrophobic than the negative ones, owing to the presence of valine and the long hydrocarbon side chain of arginine. (As mentioned above, hydrophobicsinteractions between polypeptide layers could stabilizc films to some extent.) The lengths arc consistent with published studies showing that polyions must have greater than 20;charged groups (i.e. aspartic acid and glutamic acid; lysine, arginine, and ־histidine) to be suitable for ELBL (see Kabanov, V. and Zezttt; A. Pure Appl. Chem. 56:343 and Kabanov, V. (1994) Polym. Sci. 36:143, both of which ;י are incorporated by reference herein in their entireties).
<td> Tyr</td><td> Glu</td><td> Glu</td><td> Asp</td><td> Glu</td><td> Cys</td><td> Gin</td><td colspan="4"> Asp Gly Glu Glu</td><td> Asp</td><td> Glu</td><td colspan="2"> Cys Gin</td><td> (SEQ</td><td> ID</td><td> NO:</td><td> 2)</td>
<td> Asp</td><td> Gly</td><td> Glu</td><td> Glu</td><td> Asp</td><td> Glu</td><td> Cys</td><td> Gin</td><td> Asp</td><td> Gly</td><td> Glu</td><td> Glu</td><td> Asp</td><td> Glu</td><td> Cys</td><td></td><td></td><td></td><td></td>
<td> Gin</td><td> Asp</td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td> w</td><td></td><td></td><td></td><td></td><td></td><td></td><td></td>
<td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td> .sss-ssg.</td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td>
<td> Tyr</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Ser</td><td> Vai</td><td> Gin</td><td> Gly</td><td> Arg;</td><td> Arg</td><td colspan="2"> Arg Arg</td><td> Ser</td><td> Vai</td><td> (SEQ</td><td> ID</td><td> NO:</td><td> 1)</td>
<td> Gin</td><td> Gly</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Ser</td><td> Vel</td><td> Gin</td><td colspan="2"> Gly Arg</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Ser</td><td></td><td></td><td></td><td></td>
<td> Vai</td><td> Gin</td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td>
<td> Tyr</td><td> Glu</td><td> Glu</td><td> Asp</td><td> Glu</td><td> Cys</td><td> Gin</td><td> Asp</td><td> Gly</td><td> Glu;</td><td> {Glu</td><td> Asp</td><td> Glu</td><td> Cys</td><td> Gin</td><td> (SEQ</td><td> ID</td><td> NO:</td><td> 4)</td>
<td> Asp</td><td> Gly</td><td> Glu</td><td> Glu</td><td> Asp</td><td> Glu</td><td> Cys</td><td> Gin</td><td> Asp</td><td> Gly</td><td> Glu׳</td><td> Glu</td><td> Asp</td><td> Glu</td><td> Cys</td><td></td><td></td><td></td><td></td>
<td> Gin</td><td> Asp</td><td> Gly</td><td> Glu</td><td> Glu</td><td> Asp</td><td> Glu</td><td> Cys</td><td> Gin</td><td> Asp</td><td> Gly</td><td> Glu</td><td> Glu</td><td> Asp</td><td> Glu</td><td></td><td></td><td></td><td></td>
<td> Cys</td><td> Gin</td><td> Asp</td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td>
<td> Tyr</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Ser</td><td> Vai</td><td> Gin</td><td> Gly</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Ser</td><td> Vai</td><td> (SEQ</td><td> ID</td><td> NO:</td><td> 3)</td>
<td> Gin</td><td> Gly</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Ser</td><td> Vai</td><td> Gin</td><td> Gly</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Ser</td><td></td><td></td><td></td><td></td>
<td> Vai</td><td> Gin</td><td> Gly</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Ser</td><td> Vai</td><td> Gin</td><td> Gly</td><td> Arg</td><td> Arg</td><td> Arg</td><td> Arg</td><td></td><td></td><td></td><td></td>
<td> Ser</td><td> Vai</td><td> Gin</td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td><td></td>
[0112] The amino acid residues are represented by the three-letter code given above. One glycine was introduced between each 7-rcsidue motif to inhibit secondary structure formation. Glycine was selected for this purpose because it allows the greatest variability in combination of dihedral angles (see Ramachandran, G. N. and Saisekharan, V. (1968), Adv. Protein Chemistry, 23:283, which is incorporated by reference herein in its entirety) and has a low helix propensity (0.677) and low sheet propensity (0.766). Alternatively, proline could be substituted for glycine between motifs on the basis of calculated structure propensities. Additionally, a single tyrosine was included at the N-terminus of each peptide for concentration determination by UV absorption at 280 nm.
[0114] a. Experimental demonstration
[0115] i. Materials
[0116] QCM electrodes (USI-System, Japan) coated with evaporated silver had a surface area of 0.16±0.01 cm<sup>2</sup> on each side, a resonant frequency of 9 MHz (ΛΤ-cut), and a long-term stability of ±2 Hz. lite polypeptide molecular weight was verified by electrospray mass spectrometry. Peptide purity was greater than 70%. The polypeptide buffer was 10 mM sodium phosphate or 10 mM I’ris-HCl, 1 mM DTT, 0.1 mM sodium azide, pH 7.4. All chemicals other than polypeptides were purchased from Sigma-Aldrich (USA).
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[0117] ii. Procedures
[0118] Experiments were done using pairs of designed polypeptides, one negative and one positive. Multilayer films consisting of at least 5 bi-layers of the above-identified SP2, SN1, LP4, and LN3 were deposited onto the QCM resonators using standard ELBL techniques (a bi-layer consists of one layer of polycation and one layer of polyanion). The polypeptide concentration used for layer adsorption was 2 mg-mL'<sup>1</sup>. It is known that dependence of polyion layer thickness on polyelectrolyte concentration is not strong (see Lvov, Y. and Decher, G. (1994) Crystallog. Rep. 39:628, which is incorporated herein by reference in its entirety); in the concentration range 0.1 to 5 mg mL'<sup>1</sup>, bilayer thickness was approximately independent of concentration for PSS/ PAH. By contrast, polypeptide thin films appear substantially less thick than those fabricated using high molecular weight PSS/PAH (mass calculated using Af data using the well-known Sauerbrey equation); see Lvov, Y. and Decher, G. (1994) Crystallog. Rep. 39:628. This follows from calculating film thickness on the basis of mass deposited, as is ordinarily done in the art for proteins. The calculated thickness for the designed polypeptide assembly shown in FIG. 3(c) is greater than the end-to-end length of the peptides used to make the film. DTT was included at 1 mM to inhibit disulfide bond formation. The adsorption time was 20 mm-,. utes. v
[0119] Resonators were rinsed for 1 min. in purc^water between subsequent adsorption cycles (removing ,perhaps 10-15% of weakly adsorbed material) and dried in aistream : of gaseous N<sub>2</sub>. Then the mass of the deposited pcptidd.was^ ״ measured indirectly by QCM. '!ίο mass smeasurcmcnt’ includes some water, despite drying, and lowamass ionsslike K<sup>+</sup>, Na<sup>+</sup>, and Cl'. Partial interpenetration of.ncighboring layers of peptide is probable (see Decher, G. (1997) Science 227:1232; Schmitt et al. (1993) Macromolecules •26:1058, and Korneev et al. (1995) Physica B 214 954); this could be important for the efficiency of disulfide “locking.” <sup>Λ</sup>
[0120] iii. Results
[0121] After adsorption of the polypeptide and rinsing and drying the QCM resonator, the resonant frequency of the resonator was measured. This enabled calculation of the frequency shift on adsorption and change in adsorbed mass. A decrease in frequency indicates an increase in adsorbed mass. The results are provided in FIGS. 3(a) and 3(b). FIG. 3(a) shows a comparison of adsorption data for LP4 and LN3 in different buffers (10 mM sodium phosphate, pH 7.4, 1 mM DTI’ and 10 mM Tris-HCl, pH 7.4, 1 mM DTP). It is clear from these data that adsorption depends more on the properties of the peptides than the specific properties of the buffer used. FIG. 3(b) shows resonator frequency versus adsorbed layer for different combinations of SP2, SN1, LP4, and LN3 (namely, SP2/SN1, SP2/LN3, LP4/SN1, and LP4/ LN3) in 10 mM sodium phosphate, pH 7.4 and 1 mM DTT (the lines merely connect experimental data points). Each of these combinations involved one negative polypeptide and one positive polypeptide, as required by ELBL. FIG. 3(c) shows a graph of calculated adsorbed mass versus layer number for SN1 and LP4 in 10 mM Tris-HCl, pH 7.4 and 1 mM DTT (calculated from experimental data using the Sauerbrey equation). The total adsorbed mass, approximatcly 5 pg, corresponds approximately to 1 nmol of peptide. The equation used for this calculation was 4m=0.87T0<sup>9</sup>־Af, where m is mass in grams and f is frequency in Hz (see Lvov, Y, Ariga, K., Ichinose, I., and Kunitake, T.
(1995) J, Am. Chem. Soc. 117:6117 and Sauerbrey, G. (1959) Z. Physik 155:206, both of which are incorporated herein by reference in their entireties). Film thickness, d, is estimated as d=-0.016Af, where d is in nm (see Yuri Lvov, “Electrostatic Layer-by-Layer Assembly of Proteins and Polyions” in Protein Architecture: Interfacial Molecular Assembly and Immobilization Biotechnology, (Y. Lvov & H. Mohwald eds., 2000) (New York: Dekker, 2000) pp. 125167, which is incorporated herein by reference). The line in FIG. 3(c) is a linear fit to experimental data points. The linearity of the data is a likely indicator of precise, regular assembly during adsorption and an approximately uniform density of the polypeptides in each adsorbed layer. Adsorption occurred with a frequency shift of -610±60 Hz (cations) or -380±40 Hz (anions). Linear growth of deposited polypeptide mass indicates repeatability of adsorption steps early in the assembly process and the general success of the multilayerfabrication process.
[0122]....iv. Conclusions
[0123] The above results show that polypeptides designed using the^melhod ohthe present invention are suitable for ELBL, despite significant qualitative differences from PSS and PAH, flexible homopolymers having 1 charge per unit lengtbat pH 7.4. The charge per unit length on poly-L-lysine and poly-L-glutamic acid is 1 at pH 7.4, as with PSS and PAH, but both of these polypeptides have a marked propensity to form a-helical structure under various conditions, ,making them substantially less suitable for multilayer assembly when control over thin film structure is desired. 'Hie monodisperse polypeptides of the present invention, however, enable the practitioner to know, quite precisely, the structure of the material being used for ELBL. Moreover, usual commercial preparations of poly-L-lysine and polyL-glutamic acid are polydispersc, and poly-L-lysinc, polyL-glutamic acid, PSS, and PAH evoke an immune response (i.e. are immunogenic) in humans.
[0124] Because the designed polypeptides are readily adsorbed on an oppositely charged surface, as demonstrated by experiment, there is no need for a “precursor” layer. As is known in the art, “precursor” layers are deposited on a substrate to enhance adsorption of less adsorptive substances. The lack of a precursor layer enhances the biocompatibility of the polyion films because polymers ordinarily used as precursors are immunogenic or allow less precise control over polymer structure or thin film structure than designed polypeptides.
[0125] Multilayers of the designed polypeptides were stable at the pH of human blood, 7.4. Thus, the multilayers should be useful for a broad range of biological applications. Adsorption of the designed polypeptides, each of less than 1 charge per residue, was essentially complete in less than 10 min. at 2 mg/mL and low ionic strength. This implies that these polypeptides can be used to form multilayer films quickly and with relative ease. Drying the peptide film with N<sub>2(b:)</sub> after deposition of each layer did not impair assembly. Drying is done to get an accurate QCM frequency measurement, but is not required for assembly.
[0126] The film assembly experiments were done at a lower ionic strength than that of blood, but the process gives a qualitatively similar result at higher ionic strength. The chief difference is the amount of peptide deposited per adsorption layer—the higher the ionic strength, the greater
US 2005/0069950 Al
Mar. 31, 2005 the amount of peptide deposited. This is illustrated by the graph in FIG. 7, which shows the amount of material deposited as a function of ionic strength—the peptides used were poly-L-glutamic acid and poly-L-lysinc. QCM resonant frequency is plotted against adsorption layer. The average molecular mass of poly-L-glutamate was 84,600 Da, while that of poly-lys was 84,000 Da. The peptide concentration used for assembly was 2 mg/mL. The data indicate salt concentration (ionic strength of solution) influences thin film assembly. In general, the amount of material deposited per layer increases with ionic strength in the range
Moreover, the polypeptide film assembly process can be mechanized, once the details of the various steps have been sufficiently determined.
2. Example 2
Experiments Involving De Novo-Designed Polypeptides Containing Cysteine
[0130] a. Polypeptides
[0131] The polypeptides used were:
<td> Tyr</td><td> Lys Cys Lys</td><td> Gly Lys Vai</td><td> Lys</td><td> Val Lys Cys Lys Gly</td><td> Lys Val</td><td> (SEQ ID NO: 5)</td>
<td> Lys Vai</td><td> Vai Lys Cys Lys</td><td> Lys Gly Lys</td><td></td><td> «Lys Val Lys Cys Lys</td><td> Gly Lys</td><td></td>
<td> Tyr</td><td> Glu Cys Glu</td><td> Gly Glu Vai!</td><td rowspan="2"> Ip<sup>1</sup>«! vlij</td><td> Val'Glu Cys Glu Gly</td><td> Glu Val</td><td> (SEQ ID NO: 6)</td>
<td> Glu Vai</td><td> Vai Glu Cys Glu</td><td> Glu Gly’Glu</td><td> |Giu<sup>;</sup>’Val Glu Cys Glu</td><td> Gly Glu</td><td></td>
0-100 mM NaCl. As the essential character of EI.BL'witH” designed polypeptides appears not to depend on the choice of buffer under conditions of relatively high net chaige.per , unit length and low ionic strength, qualitatively«, similar results are expected at the ionic strength ofjhumansblood. Thus, the choice of buffer should not fundamentally alterthe stability of the multilayers in thei»5target environment. However, even if the choice of buffer did affect thestability of the multilayers, the “locking” mechanism would be available as a design feature to stabilize the capsule.
[0127] The greater apparent deposition of positive polypeptides than negative ones may result from the higher charge per unit length on the positive polypeptides at pH 7.4. The material deposited in each layer probably corresponds to that required for neutralization of the charge of the underlying surface. Hydrophobic interactions could also help to explain this feature of adsorption behavior.
[0128] The usual thin film thickness calculation for proteins and other polymers is probably invalid for short polypeptides (calculated thickness is 60-90 nm, but summed length of 10 polypeptides is approximately 120 nm). This probably results from a high density of packing of the relatively short polypeptides onto the adsorption surface; the result is also consistent with finding that film thickness varies with ionic strength, as changes in structural properties of a polymer will occur and screening of charges by ions will reduce intra-layer charge repulsion between adsorbed peptides. The thickness of the designed polypeptide thin film discussed here is estimated at 20-50 nm.
[0129] Many aspects of the design and fabrication cycles could be automated. For example, a computer algorithm could be used to optimize the primary structure of peptides for ELBL by comparing predicted peptide properties with observed physical properties, including structure in solution, adsorption behavior, and film stability at extremes of pH.
[0132] Unlike the other polypeptides used in the experiments described herein, these two were not designed using human genome information; they were designed for the sole purpose of assessing the role of disulfide bond formation in polypeptide film stabilization.
[0133] b. Procedures
[0134] All experiments were conducted at ambient temperature.
[0135] All assembly experiments using QCM were conducted in the same conditions, except that the samples to undergo oxidation were dried using air instead of nitrogen gas. The assembly conditions were 10 mM Tris-HCl, 10 mM DTI’, pH 7.4. The nominal peptide concentration was 2 mg/ml. The number of layers formed was 14.
[0136] Disulfide locking conditions for the oxidizing samples were 10 mM Tris-HCl, 1% DMSO, saturation of water with air, pH 7.5. The duration of the “locking” step was 6 hours. Conditions for the reducing samples were 10 mM Tris-HCl, 1 mM DTT, saturation of water with nitrogen, pH 7.5. The duration of this step was 6 hours.
[0137] All disassembly experiments using QCM were conducted in the same conditions, except that the oxidizing samples were dried using air instead of nitrogen. Disassembly conditions were 10 mM KC1, pH 2.0 Samples were rinsed with D.l. water for 30 seconds prior to drying.
[0138] Three different types of experiments were conducted: (1) Reducing—no treatment: disassembly was conducted immediately after assembly; (2) Reducing—6 hours, as described above for reducing samples; and (3) Oxidizing—6 hours, as described above for oxidizing samples.
[0139] c. Results
[0140] The results are illustrated in FIG. 10. In the first two experiments (both reducing), all of the deposited mateUS 2005/0069950 Al
Mar. 31, 2005 rial (100%) disassembled within 50 minutes. By contrast, in the oxidizing experiment, a substantial amount of material remained after substantial'incubation of the peptide filmcoated QCM resonator at pH 2 for over 5 hours. The stability of the polypeptide films at acidic pH is determined by the conditions of assembly; in this way, film or capsule stability is a design feature that becomes possible by using polypeptides as the polyelectrolytes for ELBL.
[0141] d. Conclusions
[0142] Electrostatic forces play a key role in holding together oppositely-charged layers of designed polypeptides. At acidic pH, the net charge on one of the peptides is neutralized and the polypeptide film disassembles due to electrostatic repulsion. Reducing conditions prevent disulfide bond formation. Therefore, the electrostatic attraction between the layers is the only binding force for stabilizing the layers under these conditions. By contrast, under oxidizing conditions disulfide bonds are formed. At acidic pH, disulfide bonds inhibit film disassembly. The results indicate that layer stability at acidic pH is directly affected by the formation of intra- and/or inter-layer disulfide bonds—i.e. between molecules in the same layer, between molecules in adjacent layers, or both. This is illustrated by the results shown in FIG. 10—due to disulfide locking, more than 30% I of the film remained stable at acidic pH, despite electrostatic repulsion at relatively low ionic strength. Peptides with more cysteine residues are anticipated to further improve disulfide locking efficiency. Moreover, adjustmenffiof the ‘ conditions of peptide assembly will be an important aspect ! of engineering films to have the desired phystcal:as well as,, chemical and biological properties.
3. Exampk 3
Experiments Involving Designed Polypeptides Containing Cysteine
[0143] a. Materials
[0144] The essential elements of this experiment were a quartz crystal microbalance instrument; silver-coated resonators (9 MHz resonant frequency); the negative 48-residue peptide (LN3) (SEQ ID NO: 4); and a positive 48-residue peptide named “SP5” of the following sequence:
SP5 and LN3 by adding 4 mg of each peptide to 2 mL of the above buffer solution and adjusting the pH of each solution to 7.4; the peptide concentration was 2 mg-ml.<sup>1</sup>־.
[0146] b. Procedure for Monitoring Assembly of Polypeptide Layers on QCM Resonators
[0147] Reducing procedures were as follows: (1) The frequency of the resonator was measured and recorded prior to peptide adsorption; (2) The resonator was dipped into the SP5 peptide solution for 20 min.; (3) The resonator was dipped into the SP5 rinse solution for 30 sec.; (4) The resonator was removed from the rinse solution and dried using nitrogen gas; (5) The QCM resonant frequency of the resonator was recorded; (6) The resonator was dipped into the LN3 peptide solution for 20 min.; (7) The resonator was dippedsinto the LN3 rinse solution for 30 sec.; (8) The resonator 1-was removed from the rinse solution and dried using nitrogen gas; (9) The QCM resonant frequency of the resonator^was recorded; (10) Steps 2 through 9 were repeated until 16 layers were adsorbed onto the resonator.
V </ H
[0148] Oxidizing procedures were the same as the reducing procedures, except that the resonator was rinsed in D.l. water instead of the SP5 buffer or the LN3 buffer and dried with air instead of nitrogen before each measurement.
[0149] c. Locking Procedures
[0150] Reducing procedures were as follows: The resonator was placed in an aqueous solution containing 1 mM DTT for 6 hours. DTI’, a reducing agent, inhibited disulfide bond formation.
[0151] Oxidizing procedures were as follows: The resonator was placed in an air-saturated aqueous solution containing 1% DMSO for 6 hours. DMSO, an oxidizing agent, promoted disulfide bond formation.
[0152] d. Disassembly on Resonator
[0153] i. Solutions
[0154] Reducing conditions were as follows: 10 mM KC1, 1 mM DTT, pH 2.
Tyr Lys Gly Lys Lys Ser Cys His Gly Lys Gly Lys Lys Ser Cys (SEQ ID NO:
7)
His Gly Lys Gly Lys Lys Ser Cys His Gly Lys Gly Lys Lys Ser
Cys His
[0145] Like the other designed peptides discussed above in Part V11(E)(1), SP5 was designed using the process described above in Part VII(B)(1) to analyze the amino acid sequence of the human blood protein lactotransferrin (gi|4505043). The ELBL buffer was 10 mM Tris, pH 7.4,10 mM NaCI, and 1 mM DTT. The disassembly buffer was 10 mM KC1, pH 2. 2 mL peptide solutions were prepared for
[0155] Oxidizing conditions were as follows: 10 mM KC1, 20% DMSO, pH 2.
[0156] ii. Procedure for Disassembly
[0157] Reducing procedures were as follows: (1) The initial resonant frequency of the resonator was measured by QCM and recorded; (2) The resonator was dipped into the
US 2005/0069950 Al
Mar. 31, 2005 reducing disassembly solution for 5 min.; (3) The resonator was rinsed in reducing buffer solution for 30 see.; (4) The resonator was dried with gaseous N<sub>2</sub>; (5) The resonant frequency of the resonator was measured by QCM and recorded; (6) Steps 2 through 5 were repeated for reading times of 5, 10, 15, 20, 30, 60, and 90 min.
[0158] Oxidizing procedures were the same as for reducing procedures, except that rinsing of the resonator was done in D.I. water saturated with air instead of reducing buffer.
[0159] e. Results
[0160] FIG. 8 shows approximately linear increase in mass deposited during thin film assembly of SP5 and LN3. Both resonators show almost identical deposition of mass throughout the process of assembly, despite differences in assembly conditions.
[0161] FIG. 9 shows the percentage of material remaining during film disassembly. The layers subjected to oxidizing conditions showed a minimal loss of material at acidic pH with almost 90 to 95% of mass retention. By contrast, layers subjected to reducing conditions lost almost all the film material within the first 5 minutes of exposure to acidic pH.
[0162] f. Conclusions
[0163] The results demonstrate that at acidic pH, disulfide bonds prevent layer degeneration and hold the layers firmly together. Layer stability at acidic pH is directly affected by the formation of intra- and/or inter-layer disulfide bonds. Disulfide bond formation is dependent on the concentration and proximity of cysteine residues to each other. Increasing the concentration per unit chain length of the polypeptide would therefore directly influence disulfide bond formation and thin film stability. Increasing the ionic strength of the buffer solutions used for film assembly influences the concentration of cysteine in the film by increasing the amount of material deposited per adsorption cycle and the thickness of each layer. The increased number of cysteine amino acids in a single layer would in this way increase the number of disulfide bonds formed, and, on oxidation, increase film stability.
[0164] Other: embodiments of the invention are possible and modifications may be made without departing from the spirit and scope of the invention. Therefore, the detailed description above is not meant to limit the invention. Rather, the scope of.the invention is defined by the appended claims.
<img file="IL190885A_D0041.tif" />
SEQUENCE LISTING Xj. .
<160> NUMBER OF SEQ ID NOS: 8 <210> SEQ ID NO 1 <211> LENGTH: 32 <212> TYPES PRT \ <213> ORGANISM: Artificial Sequence <sup>w</sup> <220> FEATURE:
<223> OTHER INFORMATION: The sequence wa'8»|8ynthesi2ed and designed completely on the basis of human genome information.
<400> SEQUENCE: 1
Tyr Arg Arg Arg Arg Ser Vai Gin Gly Arg Arg Arg Arg Ser Vai Gin
10 15
Gly Arg Arg Arg Arg
Ser Vai Gin Gly Arg Arg Arg Arg Ser Vai Gin
30 <210> SEQ ID NO 2 <211> LENGTH: 32 <212> TYPE: PRT <213> ORGANISM: Artificial Sequence <220> FEATURE:
<223> OTHER INFORMATION: The sequence was synthesized and designed completely on the basis of human genome information.
<4 00> SEQUENCE: 2
Tyr Glu Glu Asp Glu Cys Gin Asp Gly Glu Glu Asp Glu Cys Gin Asp
10 15
Gly Glu Glu Asp Glu Cys Gin Asp Gly Glu Glu Asp Glu Cys Gin Asp
25 30 <210> SEQ ID NO 3 <211> LENGTH: 48 <212> TYPE: PRT <2 13> ORGANISM: Artificial Sequence <220> FEATURE:
<223> OTHER INFORMATION: The sequence was synthesized and designed completely on the basis of human genome information.
US 2005/0069950 Al
Mar. 31,2005
-continued <4 00> SEQUENCE:
Tyr Arg Arg Arg 1
Gly Arg
Arg Arg
Gly Arg
Arg Arg 35
Arg Ser 5
Arg Ser
Arg Ser
Vai Gin
Vai Gin
Vai Gin
Gly Arg
Gly Arg
Gly Arg
Arg Arg
Arg Arg
Arg Arg
Arg Ser
Arg Ser
Arg Ser 45
Vai Gin 15
Vai Gin
Vai Gin <210> SEQ ID NO 4 <211> LENGTH: 48 <212> TYPE: PRT <213> ORGANISM: Artificial Sequence <220> FEATURE:
<223> OTHER INFORMATION: The sequence was synthesized and designed; completely on the basis of human genome information.
<400> SEQUENCE: 4
<td colspan="2"> Tyr Glu Glu Asp 1</td><td> Glu 5</td><td> Cys</td><td> Gin</td><td> Asp</td><td> Gly</td><td> Glu 10</td><td> Glu</td><td> Asp Glu</td><td> Cys Gln^Asp; 15</td>
<td colspan="2"> Gly Glu Glu Asp 20</td><td> Glu</td><td> Cys</td><td> Gin</td><td> Asp</td><td> Gly 25</td><td> Glu</td><td> Glu</td><td> Asp Glu</td><td> Cys Gln>Asp 30</td>
<td colspan="2"> Gly Glu Glu Asp 35</td><td> Glu</td><td> Cys</td><td> Gin</td><td> Asp 40</td><td> Gly</td><td> Glu</td><td> Glu</td><td> Asp Glu 45</td><td> CysfeGln Asp</td>
<td> <210> <211> <212> <213> <220></td><td> SEQ ID NO LENGTH: 32 TYPE: PRT ORGANISM: FEATURE:</td><td colspan="5"> 5 1 Artificial Sequence</td><td></td><td></td><td></td><td></td>
<223> OTHER INFORMATION: The sequence was^designed de novo and synthesized.
<400> SEQUENCE: 5
Tyr Lys Cys Lys Gly Lys Vai Lys Vai Lys CyS’-Lys Gly Lys VaiLys
5 1015
Vai Lys Cys Lys Gly Lys Vai Lys Vai Lys Cys Lys Gly Lys VaiLys
2530 <210> SEQ ID NO 6 <211> LENGTH: 32 <212> TYPE: PRT <213> ORGANISM: Artificial Sequence <220> FEATURE:
<223> OTHER INFORMATION; The sequence was designed de novo and synthesized.
<400> SEQUENCE: 6
Tyr Glu Cys Glu Gly Glu Vai Glu Vai 1 5
Glu Cys Glu Gly Glu Vai Glu 10 15
Vai Glu Cys Glu Gly Glu Vai Glu Vai Glu Cys Glu Gly Glu Vai Glu
25 30 <210> SEQ ID NO 7 <211> LENGTH: 32 <212> TYPE: PRT <213> ORGANISM: Artificial Sequence <220> FEATURE:
<223> OTHER INFORMATION: The sequence was synthesized and designed completely on the basis of human genome information.
US 2005/0069950 Al
Mar. 31, 2005
-continued <4 00> SEQUENCE: 7
Tyr Lys Gly Lys Lys Ser Cys His 15
Gly Lys Gly Lys Lys Ser Cys His
Gly Lys Gly Lys Lys Ser Cys Hie
1015
Gly Lys Gly Lys Lys Ser Cys His
2530 <210> SEQ ID NO 8 <211> LENGTH: 23 <212> TYPE: PRT <213> ORGANISM: Homo sapiens <400> SEQUENCE: B
Asp Ser His Ala Lys Arg His His Gly Tyr Lys Arg Lys His Glu Lys 15 10 15
His His Ser His Arg Gly Tyr
What is claimed is:
1. A method for identifying, in amino acid sequence :־» information, and recording a desired number of amino acid’ X sequence motifs having a defined length and a net charge of * a certain polarity for use in electrostatic layer-by-layer self , assembly, comprising the steps of:
a. Obtaining an amino acid sequence for a peptide or a protein from a particular organism;
b. Locating a starter amino acid» in said amino'iacid sequence;
c. Examining said starter amino acid andjthe following n amino acids to determine the number oficharged amino acids having a polarity opposite said certain=»polarity;
d. If the number of said charged amino acids having a polarity opposite said certain polarity is one or more, continuing the method at step g;
e. Examining said starter amino acid and the following n amino acids to determine the number of charged amino acids having said certain polarity;
f. If the number of charged amino acids having said certain polarity is equal to or greater than x, recording the amino acid sequence motif consisting of said starter amino acid and the following n amino acids;
g. Locating another starter amino acid in said amino acid sequence; and
h. Repeating the method beginning at step c until the desired number of amino acid sequence motifs have been identified or all of the amino acids in said amino acid sequence have been used as said starter amino acid in step c;
wherein x is greater than or equal to approximately one-half of n.
2. The method of claim 1, wherein n is less than or equal to 11, but greater than or equal to 3:
3. The method of claim 1, wherein n=8 and x=5.
4. The method of claim 1, wherein n=6 and x=4.
<sup>:</sup> 5. The method of claim 1, wherein at least one of said recorded amino acid sequence motifs comprises cysteine.
6. A^method for designing a polypeptide for use in electrostatic layer-by-layer self assembly, comprising the steps of:
a. Identifying, in amino acid sequence information, and recording one or more amino acid sequence motifs having a defined length and a net charge of a certain polarity using the following steps:
i. Obtaining an amino acid sequence for a peptide or a protein from a particular organism;
ii. Locating a starter amino acid in said amino acid sequence;
iii. Examining said starter amino acid and the following n amino acids to determine the number of charged amino acids having a polarity opposite said certain polarity;
iv. If the number of said charged amino acids having a polarity opposite said certain polarity is one or more, continuing the method at step vii;
v. Examining said starter amino acid and the following n amino acids to determine the number of charged amino acids having said certain polarity;
vi. If the number of charged amino acids having said certain polarity is equal to or greater than x, recording the amino acid sequence motif consisting of said starter amino acid and the following n amino acids;
vii. Locating another starter amino acid in said amino acid sequence; and viii. Repeating the method beginning at step iii until the desired number of amino acid sequence motifs have been identified or all of the amino acids in said amino acid sequence have been used as said starter amino acid in step iii;
wherein x is greater than or equal to approximately one-half of n; and
US 2005/0069950 Al
Mar. 31, 2005
b. Joining a plurality of said recorded amino acid sequence motifs to form a polypeptide.
7. The method of claim 6, wherein n is less than or equal to 11, but greater than or equal to 3.
8. The method of claim 6, wherein n=8 and x5־־.
9. 'Hie method of claim 6, wherein n=6 and x=4.
10. The method of claim 6, wherein at least one of said plurality of joined amino acid sequence motifs comprises cysteine.
11. The method of claim 6, wherein at least one of said plurality of joined amino acid sequence motifs has a summed a-helix propensity of less than 7.5 and a summed β-sheet propensity is less than 8.
12. The method of claim 6, further comprising the step of including in the polypeptide a functional domain.
13. The method of claim 6, wherein said amino acid sequence comes from the proteome of said organism.
14. The method of claim 13, wherein said amino acid sequence comes from a blood protein from said organism.
15. The method of claim 14, wherein said organism is a human.
16. The method of claim 14, wherein at least one of said plurality of joined amino acid sequence motifs comprises the if sequence described in SEQ ID NO: 1.
17. The method of claim 14, wherein at least one of said plurality of joined amino acid sequence motifs comprises the. sequence described in SEQ ID NO: 2.
18. The method of claim 14, wherein at least one^f said . ., plurality of joined amino acid sequence motifs comprises the sequence described in SEQ ID NO: 3:
19. The method of claim 14, wherein atleast one of said plurality of joined amino acid sequence motifs’eomprises the sequence described in SEQ ID NO 4.s.!>,.
20. The method of claim 14, wherein at least one of said plurality of joined amino acid sequence motifs comprises the sequence described in SEQ ID NO: 7.
21. A thin film, said film comprising a plurality of layers of polypeptides, said layers of polypeptides having alternating charges, wherein at least one of said polypeptides comprises one or more amino acid sequence motifs consisting of n amino acids, at least x of which are positively charged and none is negatively charged, or at least x of which are negatively charged and none is positively charged, wherein x is greater than or equal to approximately one-half of n.
22. The thin film of claim 21, wherein said at least one of said polypeptides comprises non-natural amino acids.
23. The thin film of claim 21, wherein said thin film further comprises at least one antimicrobial polypeptide.
24. The thin film of claim 23, wherein said antimicrobial polypeptide comprises the sequence described in SEQ ID NO: 8.
25. The method of claim 21, wherein said at least one of said polypeptides comprises a functional domain.
26. The thin film of claim 21 wherein said at least one amino acid sequence motif is identified by the method of:
a. Obtaining an amino acid sequence for a peptide or a protein from a particular organism;
b. locating a starter amino acid in said amino acid sequence;
c. Examining said starter amino acid and the following n-1 amino acids to determine the number of charged amino acids having a polarity opposite said certain polarity;
d. If the number of said charged amino acids having a polarity opposite said certain polarity is one or more, continuing the method at step g;
c. Examining said starter amino acid and the following n-1 amino acids to determine the number of charged amino acids having said certain polarity;
f. If the number of charged amino acids having said certain polarity is equal to or greater than x, recording the amino acid sequence motif consisting of said starter amino acid and the following n-1 amino acids;
Afi.'
g. Locating another starter amino acid in said amino acid sequence;,and
h. Repeating the, method beginning at step c until the : desired number pf amino acid sequence motifs have been identified dr all of the amino acids in said amino acid sequence have been used as said starter amino acid <sup>i-</sup> in *step’iii;
wherein x is greater than or equal to approximately « one-half of n.
.27. The thin film of claim 26, wherein n is less than or equal to 12, but greater than or equal to 4.
28. The thin film of claim 26, wherein n=9 and x=5.
29. The thin film of claim 26, wherein n=7 and x=4.
30. The thin film of claim 26, wherein said at least one amino acid sequence motif comprises cysteine.
31. The thin film of claim 26, wherein said at least one amino acid sequence motif has a summed a-helix propensity of less than 7.5 and a summed β-sheet propensity of less than 8.
32. The thin film of claim 26, wherein said at least one amino acid sequence motif is comprised of human blood proteins.
33. The thin film of claim 26, wherein said at least one amino acid sequence motif comprises the sequence described in SEQ ID NO: 1.
34. The thin film of claim 26, wherein said at least one amino acid sequence motif comprises the sequence described in SEQ ID NO: 2.
35. The thin film of claim 26, wherein said at least one amino acid sequence motif comprises the sequence described in SEQ ID NO: 3.
36. The thin film of claim 26, wherein said at least one amino acid sequence motif comprises the sequence described in SEQ ID NO: 4.
37. The thin film of claim 26, wherein said at least one amino acid sequence motif comprises the sequence described in SEQ ID NO: 7.
38. The thin film of claim 26, wherein said thin film forms a microcapsule.
39. The thin film of claim 38, wherein said microcapsule comprises a core, and said core comprises hemoglobin.
40. The thin film of claim 39, wherein said hemoglobin is in crystallized form.
41. The thin film of claim 39, wherein said hemoglobin is in liquid form.
US 2005/0069950 Al
Mar. 31, 2005
42. The ihin film of claim 38, wherein said microcapsulc comprises a core, and said core comprises a therapeutic drug.
43. 1’he thin film of claim 42, wherein said therapeutic drug is in crystallized form.
44. The thin film of claim 42, wherein said therapeutic drug is in liquid form.
45. The thin film of claim 26, wherein said thin film is formed on a solid substrate.
46. The thin film of claim 45, wherein said solid substrate is a microparticle.
47. The thin film of claim 45, wherein said substrate is a medical implant.
48. A method for designing polypeptides for use in electrostatic layer-by-layer self assembly comprising the following steps:
a. Designing de novo a plurality of amino acid sequence motifs, wherein at least one of said amino acid sequence motifs consists of π amino acids, at least x of which are positively charged and none is negatively charged, or at least x of which are negatively charged and none is positively charged, x is greater than or equal to approximately one-half of n; and
b. Joining said plurality of said amino acid sequence motifs to form a polypeptide.
49. The method of claim 48, wherein n is less than.or equal to 12, but greater than or equal to 4.
50. The method of claim 48, wherein n=9 and x-5.
51. '1’he method of claim 48, wherein n=6 and x=4.
52. The method of claim 48, wherein said at least one amino acid sequence motif has a summed a-helix propensity of less than 7.5 and a summed β-sheetipropensity of less than
53. The method of claim 48, wherein said at'lcast one amino acid sequence motif comprises One....or more nonnatural amino acids.
54. The method of claim 48, wherein said at least one amino acid sequence motif comprises right-handed amino acids.
55. The method of claim 48, further comprising the stop of joining at least one antimicrobial peptide along with said plurality of amino acid sequence motifs.
56. The method of claim 55, wherein said at least one antimicrobial peptide comprises the sequence described in SEQ ID NO: 8.
57. The method of claim 48, further comprising the step of including a functional domain in forming said polypeptide.
58. A method for controlling the mechanical stability and porosity of a multi-layer thin film, comprising the step of providing a multi-layer thin film, said film comprising a plurality of layers of polypeptides, said layers of polypeptides having alternating charges, wherein at least one of said layers of polypeptides comprises one or more free sulfhydryl-containlng amino acids.
59. The method of claim 58, wherein said one or more free sulfhydryl-containing amino acid is cysteine.
60. The method ofclaim 59, wherein at least one set of «7 / f ־.”1 . ץ adjacentflayerssof polypeptides comprises cysteine.
I
61. The,method of claim 58, wherein at least one of said layers of polypeptides comprises non-natural amino acids.
62. The method of claim 58, wherein at least one of said !layers of polypeptides comprises an antimicrobial peptide.
63. The method of claim 62, wherein said antimicrobial :.peptide comprises the sequence described in SEQ ID NO: 8.
64. The method of claim 58, wherein at least one of said layers of polypeptides comprises a functional domain.
65. The method of claim 58, wherein said polypeptides comprise at least one amino acid sequence motif consisting of n amino acids, at least x of which are positively charged and none is negatively charged, or at least x of which are negatively charged and none is positively charged, wherein x is greater than or equal to approximately one-half of n.
*****
<img file="IL190885A_D0042.tif" />
United States Patent [19]
Onda et al.
IIIIIIM
US006020175A
[11] Patent Number: 6,020,175
[45] Date of Patent: Feb. 1,2000
[54] MULTIPLE LAYERED FUNCTIONAL THIN FILMS
[75] Inventors: Mitsuhlko Onda; Yuri Lvov; Katsuhiko Ariga, all of Kurume; Toyokl Kunltake, Fukuoka-ken, all of Japan
[73] Assignee: Japan Science and Technology Corporation, Honcho, Japan
[21] Appl. No.: 08/926,493
[22] Filed: Sep. 10, 1997
[30] Foreign Application Priority Data
Sep. 30, 1996 [JP] Japan .................. 8-280329
[51] Int. Cl.<sup>7</sup> .............. C12N 11/00; C12N 11/08;
C07K 17/00; C07K 17/08
[52] U.S. Cl.............. 435/180; 435/174; 435/176;
435/178; 435/182; 530/402; 530/810; 530/811;
530/813; 530/815; 530/817
[58] Field of Search ................... 435/174, 176,
435/178, 180, 182; 530/402, 810, 811, 813, 815, 817
[56] References Cited
PUBLICATIONS
Biotechnology and Bioengineering article entitled “Sequential Actions of Glucose Oxidase and Peroxidase in Molecular Films Assembled by Layer-by-Layer Alternate Adsorption” vol. 51, pp. 163-167 (1996).
J.Am. Chem. Soc״ vol. 117, No. 22, pp. 6117-6123 (1995) article entitled “Assembly of Multicomponent Protein Films by Means of Electrostatic Layer-by-Layer Adsorption”.
Primary Examiner—David M. Naff
Attorney, Agent, or Finn—Fay, Sharpe, Fagan, Minnich & McKee, LLP
[57] ABSTRACT
Multiple layered functional thin films fixed on a solid support are provided which comprise multiple layers of functional molecules (such as enzymes and other proteins, pigments and dyes) admixed with polymer ions in combination with multiple layers of polymer ions without the functional molecules. The films are prepared by immersing a solid support having an electric charge in an admixed polymer ion-functional molecule solution having a net electrie charge opposite to that of the solid support followed by immersing the solid support in a polymer ion solution having a net electric charge opposite to that of the admixed polymer ion-functional molecule solution, and repeating at least once the immersings of the solid support in the solulions. Alternatively, the films are prepared by immersing the solid support in a polymer ion solution having a net electric charge opposite to that of the solid support followed by immersing the solid support in an admixed polymer ionfunctional molecule solution having a net electric charge opposite to that of the polymer ion solution, and repealing at least once the immersings of the solid support in the solutions.
Clnims, 7 Drawing Sheets
6,020,175
MULTIPLE LAYERED FUNCTIONAL THIN FILMS
FIELD OF INVENTION
The present invention relates to a functional thin film and a method of making the same, more particularly, to the preparation of a novel ultrathin film, i.e. a thin film regulated at a molecular level by the utilization of the alternate layer-by-layer method.
BACKGROUND OF THE INVENTION
Most biological reactions proceed through highly efficient and selective physical and chemical processes in which proteins such as enzymes or functional pigment molecules work singly or in a cooperative or sequential manner. In order to artificially mimic such functions for developing novel molecular devices such as enzyme reactors, biosensors or luminescent elements, it is necessary to build up a structure or assembly in which functional molecules are layered in a desired sequence. Generally, functional molecules can be layered onto a solid support by one of the following methods: (i) the LB method in which a thin film developed on the surface of a liquid is transferred onto a suppoirt, (ii) the monolayer adsorption method by which functional molecules are fixed directly on a solid support, and (iii) the alternate layer-by-layer method for fixing functional molecules through adsorption alternately with other molecular components.
The LB method is known as a method for preparing a thin film in which the molecular layers are arranged in a desired order with a precision of molecular level. The method comprises dissolving an amphiphilic substance such as a lipid in an organic solvent, spreading a monolayer on an aqueous surface and transferring the monolayer onto a solid substrate, thereby forming a thin film with a desired thickness by controlling the order of the layers. This method suffers from a restriction that it is only applicable to waterinsoluble substances having properties similar to surfactants, since the subject substance must be developed on an aqueous surface as a monolayer. In addition, the LB method has a drawback in that it has a poor productibility and requires a device which is expensive and not easy to handle.
The monolayer adsorption method is to fix molecules dissolved in a solution, onto a solid support as a monolayer taking advantage of a strong interaction such as that between silanol and glass or thiol and gold. This method is advantageous in that a water-soluble substance can be employed. It has additional merits that the resultant film is resistant to external actions because of the strong interaction between the solid support and the monolayer and that the fixation can be made regardless of the shape of the solid support. However, the method has a fatal drawback in that chemical reactions with specific functional groups are indispensable for the preparation of a multi-layered structure and thus the substances usable are restricted to those having the specific functional groups which will interact with the support material.
The alternate layer-by-layer method is to prepare a thin film through alternate adsorption of oppositely-charged substances which may be selected in combination from among organic polymer ions, inorganic polymer ions, proteins and the like. The principle of this layering method is as follows: If there is immersed in a solution of polymer ions a solid support whose surface electric charge is opposite to that of the polymer ions, the polymer ions are adsorbed onto the support due to electrostatic interaction. This results in the neutralization of the surface charge of the support by the polymer ions and then the generation of new electric charge due to overadsorption of the polymer ions. Thus, if the resultant assembly is immersed in a solution of a substance having an electric charge opposite to that of polymer ions, for example, in an aqueous solution of a protein, another new electric charge is generated on the surface due to the charge neutralization and the overadsorption. Repetition of this process will enable alternate layering of such substances as polymer ions and proteins in a desired order and substantially in an indefinite manner. The extent of the overadsorption in each step is limited by the charge saturation and thus a limited amount of the polymer ions are fixed on the surface in each step. This method is advantageously carried out in a simple manner without need for any sophisticated devices. The method is also meritorious in that it is suitable for use in the fixation of easily denaturable molecules such as proteins, since a solution of such substance can be directly employed.
However, the alternate layer-by-layer method is not applicable to the preparation of an ulttrathin film composed of non-flexible (rigid) functional molecules, wherein a nonflexible or rigid functional molecule can be defined as a functional molecule incapable of flexibly changing its conformations (special arrangements of atoms in the molecule) in compliance with the fixed electric charge of the surface onto which the molecule is to be adsorbed. For example, this method is not always useful in the preparation of an ultrathin film by layering functional molecules having a low molecular weight, since the method is based on the stabilization due to multi-site bondings. Although some cases are found in which the alternate layer-by-layer method is applied to certain types of dyes or bolaamphiphilic lipids, for stable layering such substances of a low molecular weight must be capable of associating with each other so as to behave in a manner similar to polymer ions.
Thus, the alternate layer-by-layer method cannot always be applied to a variety of low molecular-weight functional molecules. In addition, even when proteins are employed as functional molecules, particularly in layering enzymes such as glucoseoxidase, there may be a cases where no monolayer is formed because of the association of such molecules with each other in an aqueous solution. Improvement is therefore needed in the alternate layer-by-layer method to make it applicable to a wider range of functional molecules by eliminating the above-mentioned problems such as the association of the molecules.
SUMMARY OF THE INVENTION
The present invention is based on the discovery that the above-mentioned problems with respect to the alternate layer-by-layer method can be solved by mixing functional molecules with polymer ions beforehand (premixing) in a solution, and then carrying out alternate layering using the resultant solution.
The present invention thus provides a method for producing a functional thin film which comprises immersing a solid support having an electric charge in a (first) admixed polymer ion-functional molecule solution having a net electric charge opposite to that of the solid support followed by immersing the solid support in a (first) polymer ion solution having a net electric charge opposite to that of the (first) admixed polymer ion-functinal molecule solution, or alternatively immersing a solid support having an electric charge in a (second) polymer ion solution having a net electric charge opposite to that of the solid support followed by
6,020,175 immersing the solid support in a (second) admixed polymer ion-functional molecule solution having a net electric charge opposite to that of the (second) polymer ion solution, and repeating such immersing steps of the solid support in the admixed polymer ion solution and the admixed polymer ion-functional molecule solution to form a desired multilayered thin film.
In another aspect of the present invention, it provides a functional thin film which comprises multiple layers of non-flexible functional molecules and multiple layers of polymer ions fixed on a solid support. Such thin films have not hitherto been producible in any way.
DESCRIPTION OF THE DRAWINGS
FIG. 1 shows QCM frequency changes observed in the alternate layer-by-layer assembling of Examples 1 to 4.
FIG. 2 shows QCM frequency changes observed in the alternate layer-by-layer assembling of Examples 3 and 4.
FIG. 3 shows UV spectra observed in Examples 8 to 10.
FIG. 4 shows QCM frequency changes observed in the alternate layer-by-layer assembling of Examples 35 and 36.
FIG. 5 shows an increase in UV absorbance at 665 nm observed in Example 37.
FIG. 6 shows QCM frequency changes observed in the alternate layer-by-layer assembling of Examples 38 and 39.
FIG. 7 shows UV spectra observed in Examples 40 and 41.
FIG. 8 shows QCM frequency changes observed in the alternate layer-by-layer assembling of Example 42.
DESCRIPTION OF THE INVENTION
According to the present invention there is provided an ulitrathin film having a thickness of a molecular level, from a variety of molecules, ranging from low molecular weight to high molecular weight molecules, by layering such molecules in the desired number and in the desired order.
The conventional alternate layer-by-layer method is based on the foresaid principle. In the present invention, the adoption of the admixed polymer ion-functional molecule solution, instead of a simple polymer ion solution, makes it possible to layer non-flexible or rigid functional molecules in any desired number and in any desired order of the layers to form an ultrathin film of a molecular level, while such molecules have been difficult to layer in the conventional methods as they arc susceptible to association with each other, particularly in the case of proteins.
As can be seen from the above-mentioned principle, according to the present invention the admixed polymer ion-functional molecule solutions can be utilized directly in the preparation of films and hence the decomposition or denaturation of such functional molecules is avoided. Thus, the method for fixing functional molecules according to the present invention provides a remarkable technique for constructing novel functional materials, in marked contrast to the methods hitherto proposed for fixing functional molecules in which chemical modifications of the molecules are needed or denaturation of the molecules occurs and impairs the intrinsic functions of such molecules.
The method of the present invention can be applied to a wide variety of functional molecules since the molecules have only to be mixed with polymer ions to form admixed solutions and need not be modified with specific functional group to develop specific properties for the layering. For example, even materials which are generally difficult to isolate can be easily layered simply by mixing with polymer ions in solutions. In addition, rare materials generally occurring in an extremely small amount can be utilized in the form of admixed solution with polymer ions.
The present invention is also advantageous in that different types of functional molecules can be used in combination and fixed in any desired order so as to construct highly useful composite materials with multiple functions.
In the present invention there are generally employed flexible organic polymer ions as matrices for fixation and thus mass diffusion throughout the thin films is facilitated as compared with the case in which rigid components such as lipids are used as the matrices. It should however be noted that rigid organic or inorganic polymer ions can also be utilized as the fixation matrices in the present invention.
The method of the present invention for preparing thin films can be practiced in an extremely easy manner in a short period of time by simply immersing solid supports into admixed polymer ion-functional molecule solutions, without need of any sophisticated devices. Thus, any types of solid materials can be selected as supports to produce systems imparted with additional functions due to the supports.
The invention will now be described more specifically.
Polymer ions to be used in the present invention can be defined as organic polymers having functional groups with an electric charge on their molecular skeletons or branches, or inorganic polymers with an electric charge. Usable polyanions (anionic polymer ions) are generally ones having such functional groups as sulfonic acid, sulfuric acid and carboxylic acid, which are negatively chargable, and include poly(styrenesulfonate) (PSS), poly(vinylsulfatc) (PVS), dextransulfate, chondroitin sulfate, poly(acrylic acid) (PAA), poly(methacrylic acid) (PMA), poly(maleic acid), poly(fumalic acid), and montmorillonite (Mont). Polycations (cationic polymer ions) usable are ones having such functional groups as quaternary ammonium group and amino group, which are positively chargable, and include poly(ethyleneimine) (PEI), poly(allylamine hydrochloride) (PAH), poly(diallyl-dimethyl-ammonium chloride) (PPDDA), poly(vinylpyridine) (PVP) and poly(lysine). These polymer ions are all soluble in water or in a waterorganic solvent mixture. Also usable are electrocouductive polymers, functional polymer ions such as those from poly (aniline-N-propane-sulfonic acid) (PAN), and biopolymers such as deoxyribonucleic acid (RNA) and polysaccharide with an electric charge (e.g. pectin). Rigid organic polymer ions such as those deirived from polythiophene, polyanilinc and poly(phenylene vinylene) can also be used in the present invention.
All types of functional molecules are applicable in the present invention, so long as such molecules are soluble in a solution together with polymer ions as exemplified above.
Applicable in the present invention are not only such functional molecules as conventionally employed in the alternate layer-by-layer method, but also various types of non-flexible functional molecules which have been hitherto impossible to layer, thereby enabling the construction of a variety of novel functional thin films.
Examples of suitable functional molecules include proteins such as glucose oxydase (GOD; molecular weight 18600, isoelectric point 4.2), peroxydase (POD; molecular weight 42000, isoelectric point 7.2), glucoamylase (GA; molecular weight 100000, isoelectric point 4.2), alcohol dehydrogenase (ADH; molecu lar weight 100000, isoelectric point 9), diaphorase (DA; molecular weight 700000, iso6,020,175 electric point 4), cytochrome (Cyt; molecular weight 12400, isoelectiric point 10.1), lysozyme (Lys; molecular weight 14000, isoelectric point 11), histone f3 (His; molecular weight 15300, isoelectric point 11), myoglobin (Mb; molecular weight 17800, isoelectric point 7.0), and hemoglobin (Hb, molecular weight 64000, isoelectric point 6.8), which arc suitable for application in catalytic elements and sensors. As applicable functional molecules there are also included such functional pigments or dyes as mordant yellow 10 (MY 10), mordant blue 29 (MB 29), flavin adenine dinucleotide (FAD), Congo Red (CR), tctraphcnylporphinc-tctrasulfonic acid (TPPS), Acid Red 27 (AR 27), Acid Red 26 (AR 26), Acid Red 52 (AR 52), Bismarck Brown (BB), indigo carmine (IC), and Ponceau S (PS), which may be suitable for application in electroluminescent (EL) elements and other uses. Other functional molecules usable in the present invention, range widely from biopolymers, such as various receptor-proteins, to small molecules.
All types of materials can be utilized as solid supports in the present invention, so long as such materials possess an electric charge on their surfaces (e. g. silver with anionic surface, glass or quartz with anionic surface, and polymer films having a surface charge), or they are capable of being provided with an electric charge, such as gold (capable of being provided with a surface charge due to absorption of a substance such as mercapto-propionic acid) and a variety of electrodes. The fixation or self-assembling according to the present invention is based on the simple adsorption mechanism. It is therefore not indispensable that the supports have a smoothed surface, and a variety of materials can be adopted therefor. For example, porous solid materials such as filters, powdery or particulate materials such as silica gel, and resinous materials in the form of beads, as well as smooth-surfaced solid supports, can be used.
While both the admixed polymer ion-functional molecule solution and the polymer ion solution to be used in the present invention are basically aqueous solutions, they may be mixed solutions with organic solvents depending upon the solubilities of the polymer ions and the functional molecules. The concentrations of the solutions are determined by the solubilities of the functional molecules and the polymer ions in which no strict concentration adjustment is necessary since the absorption steps are based on the neutralization and resaturation of the surface charge. While concentrations may be 5 to 10 mg/ml for a functional molecule and 1 to 3 mg/ml for a polymer ion, they are not restricted to these ranges. If needed, a buffer medium or such a chemical as HCI may be added to control the pFl of the solutions and to sufficiently charge the polymer ions.
The method of the present invention for preparing a thin film is generally started with immersing a solid support alternately into two different types of organic polymer ion solutions, in whish one is a solution of polycation and the other is a solution of polyanion, so as to form layers of the flexible polymer ions on the support with the outermost being an organic polymer ion layer with an electrical charge opposite to that of an admixed functional molecule-polymer ion solution.
The thus-precoated support is then (i) immersed into the admixed polymer ion-functional molecule solution, followed by (ii) rinsing, (iii) immersion into a polymer ion solution or into the admixed polymer ion-functional moleculc solution and (iv) rinsing. The steps of (i) to (iv) arc repeated at desired times so as to produce a multi-layered ultrathin film containing the functional molecules.
In all of the steps, care must be taken to ensure that the net electrical charges of the solutions to be used for adjacent or contiguous layers are opposite to one another. In particular, the poylmer ion used in the admixed polymer ion-functional molecule solution and the polymer ion used in the polymer ion solution are different polymer ions having opposite electric charges. This leads to the construction of a multilayered thin film of self-assembly in which functional molecule layer is substantially sandwiched between the two different types of polymer ions having the opposite electric charges.
However, the polymer ion used in the admixed polymer ion-functional molecule solution and the polymer ion used in the polymer ion solution may be ones having the same electric charges—not only the same polymer ions having the same electric charges but also different polymer ions having the same electric charge. For example, negatively charged functional molecules are admixed (premixed) with positively charged polymer ions to prepare an admixed polymer ion-functional molecule solution in which the concentration of the polymer ions is relatively low so that the resultant admixed solution has a negative net electric charge, while a polymer ion solution with a positive net charge is prepared from the same polymer ions as used in the admixed polymer ion-functional molecule solution. Thus, immersions of a solid support alternately into such admixed polymer ionfunctional molecule solution and polymer ion solution result in the construction of a functional thin film composed of multi layers of the functional molecules and polymer ions.
The formation of the functional thin film of the present invention can be easily verified by appropriate analytical means, among which a quartz oscillator is particularly preferred. The quartz oscillator, known as quartz crystal microbalance (QCM), is a device which, based on change in its frequency, enables determination of the mass or weight of a substance adsorbed thereon with an accuracy of 10<sup>5</sup>־<sup></sup>grams. The presence or inclusion of functional molecules in the thin films can be verified by spectroscopic methods, for example, by UV spectral measurements.
The thin films of the present invention can be applied in a reaction system without need for any sophisticated devices. For example, when a thin film of the invention is to be used as an enzymatic clement in a liquid reaction system, the solid support with functional layers fixed thereon is simply introduced into a solution containing the substrate for the enzymatic reaction.
The present invention is described in more detail below by way of examples, which in no way limit the invention.
Examples 1-4: Layering and Fixation of MY10 Dye
Examples 1 to 4 illustrate how the present invention improves the alternate layer-by-layer method for constructing functional thin films. In these examples MY10 dye was fixed or assembled on a quartz crystal microbalancc having a silver-electrode coating thereon as a solid support to form an ultrathin film. The surface of the silver electrode (surface area: 0.2 cm<sup>2</sup>) was negatively charged because of partial oxidation. Onto the silver-electrode-coated quartz crystal were alternately fixed several layers of polycation and polyanion as a precursor coating, on which MY10 was adsorbed from an admixed polymer ion-MYlO solution in accordance with the present invention. For comparison, the alternate layering of MY10 and polycation PDDA (Example 1) and also the alternate layering of polyanion PSS and polycation PDDA were also performed in accordance with the conventional method.
FIG. 1 shows the QCM frequency changes observed in these Examples. As can be seen from the result in Example 2 (for comparison), alternate layering of the oppositely charged polymer ions produced a regularly increasing frequency change, suggesting regular growth of the film.
6,020,175 aforementioned Example 4, admixed MY10/PSS solution ([MY10]/[PSS]=10 mM/15 mM) was prepared for an alternate layer-by-layer assembling by immersing the solid support alternately in the admixed solution and in PDDA 5 solution. Alternate-layered films differing in the number of layers were prepared for UV spectral measurement. FIG. 3 illustrates the spectra of the films having 0,1,5 and 10 layers of MY10, designated as Examples 7, 8, 9 and 10, respectively. Absorption peaks are observed at around 350 nm in the spectra of the films having the dye laycr(s) as expected, <sup>10</sup> indicating the fixation of MY10 molecules within the films.
It was also found that the peak intensity increases with increasing number of the layers.
Thus, the results verify, together with the QCM data shown in FIG. 1, that the method of the invention is effective <sup>כ</sup> in the growth of the films.
Examples 11-20: Layering and Fixation of Various Dye Molecules
These examples illustrate the applicability of the present invention to a variety of dye molecules. Different types of dye molecules were layered by alternate layer-by-layer methods to make a quantitative study of film growth by means of the quartz crystal microbalance. The results are expressed in terms of average frequency changes for the respective dyes, as given in Table 1.
Examples 11, 12, 16 and 18 are films in which PSS and PDDA, MY10 and PDDA, FAD and PDDA, and MB29 and PDDA were respectively layered by the conventional alternate layer-by-layer technique. Except for Example 11 in which two different polymer ions were employed for the alternate layering, a decrease or only a slight increase in the film mass was observed in each step of cation adsorption and/or anion adsorption, suggesting the inapplicability of the conventional alternate technique to MY10, FAD or MB29.
By contrast, in the cases of Examples 13 and 14 in which admixed MY10-PSS solution was employed, Example 17 in which admixed FAD-PSS solution was employed and Example 20 in which admixed MB29-PDDA solution was employed in accordance with the present invention, a clear increase in the film mass indicative of film growth is observed in each step of anion adsorption and cation adsorption. The frequency changes in these Examples were higher than those in the alternate layering of PSS and PDDA, indicating that the dye molecules were effectively fixed <sup>45</sup> within the films.
The results thus demonstrate that a variety of dye molecules, such as those which have been difficult to layer to form a film by the conventional layer-by-layer method, can be successful layered and assembled by premixing such <sup>50</sup> dyes with polymer ions according to the present invention. There may be cases in which sufficient film growth is not obtained as in Example 15 with admixed MY10/PDDAand Example 19 with MB29/PSS. This suggests that the rcspcclive dyes should be admixed with lhe corresponding appropriate, compatible polymer ions.
However, in the case of Example 1 (for comparison) where MY10, a low molecular weight molecule, was employed together with the polymer ion, alternate increase and decrease in the film mass was observed, suggesting that the construction of an ultrathin film composed of MY10 is not feasible by the conventional alternate layer-by-layer method.
In Example 3 in accordance with the present invention, MY10 and PSS were premixed in a ratio of [MY10]/ [PSS]=1 mM/15 mM to form an admixed solution, followed by alternate layering by immersing the precursor-coated support alternately in the admixed solution and a PDDA solution.
In Example 4 in accordance with the present invention, MY10 and PSS were admixed or premixed in a ratio of [MY10]/[PSS]=10 mM/15 mM to form an admixed solution, followed by alternate layering by immersing the precursor-coated support alternately in the admixed solution and the PDDA solution. FIG. 1 also gives the frequency changes for these adsorption procedures, all of which demonstrate highly regular growth of the film. As the film <sup>20 </sup>growth rates in Examples 3 and 4 were clearly higher than that in Example 2 employing PSS and PDDA, it is clear that MY10 is included in the films in Examples 3 and 4. It is also observed that the film growth rate in Example 4 was higher than in Example 3, suggesting that the higher is the propor- 25 tion of MY10 in the admixed solution, the higher is the film growth rate. This also verifies that the increased growth rate of film in Examples 3 and 4 is based on the higher amount of MY10 adsorption. These results thus demonstrate that the admixing of MY10 dye with PSS prior to alternate layer- <sub>3U </sub>by-layer assembling step enables the growth of the films with regularly-layered structures, which have never been producible by the conventional alternate layer-by-layer method.
Examples 5 & 6: Studies on Ionic Strength and Dielectric Coefficient
In Example 5, alternate layer-by-layer assembling was attempted by immersing the solid support alternately in an aqueous MY10 solution and in an aqueous PDDA solution both containing IM NaCI. Alternate layer-by-layer assembling was also attempted, in Example 6, by the alternate immersion of the support in an aqueous MY10 solution and in an aqueous PDDA solution both containing 50% acetone. FIG. 2 shows QCM frequency changes for these examples, in which there are observed alternate increase and decrease in the film mass, suggesting that no efficient film growth was achieved. Il is thus verified lhal lhe simple change in ionic strength or dielectric constant in lhe solution will not produce any improvement over the conventional method.
Examples 7 through 10: Verification of Inclusion of MY10
These examples are to verify that MY10 molecules are actually included or present in the films of a layered structure obtained by the method of the present invention. As in
TABLE 1
<td colspan="2"> Anion Component</td><td> Frequency Change(Hz)</td><td> Calion Component</td><td> Frequency Change(Hz)</td>
<td> Example 11</td><td> 15 m M PS S</td><td> 53</td><td> 19 m Μ P D D A</td><td> 50</td>
<td> Example 12</td><td> ImMMYlO</td><td> 105</td><td> 1.9 m Μ P D D A</td><td></td>
<td> Example 13</td><td> 1 m Μ Μ Y 10/15 m Μ P S S</td><td> 163</td><td> 19 m Μ P D D A</td><td> 55</td>
<td> Example 14</td><td> 10 1» MM Y 10/15 m Μ P S S</td><td> 188</td><td> 19 m Μ P D DA</td><td> 133</td>
<td> Example 15</td><td> 15 tn M PS S</td><td> 214</td><td> 10 m Μ Μ Y 10/19 m Μ P D D A</td><td> 7</td>
<td> Example 16</td><td> 1 m M F A D</td><td> 156</td><td> 1.9 m M PDDA</td><td></td>
6,020,175
TABLE !-continued
Anion Frequency Cation Frequency
Component Changc(Hz) Component Change(llz)
<td> Example 17</td><td> 10 m M FA D/15 m M PS S</td><td> 117</td><td> 19 m Μ P D D A</td><td> 29</td>
<td> Example 18</td><td> 1 m Μ Μ B 29</td><td></td><td> 1.9 m M PD D A</td><td> 10</td>
<td> Example 19</td><td> 10 m Μ Μ B 29/15 m M PSS</td><td> 214</td><td> 19 m Μ P D D A</td><td> 34</td>
<td> Example 20</td><td> 15 m Μ P S S</td><td> 83</td><td> 10 mM Μ B 29/19 m M PDDA</td><td> 75</td>
TABLE 2
<td></td><td> Anion</td><td> Frequency</td><td> Cation</td><td> Frequency</td>
<td></td><td> Component</td><td colspan="2"> Change(Hz) Component</td><td> Changc(Hz)</td>
<td> Example 21</td><td> 1 nig/mL GOD</td><td> 2330</td><td> 1 nig/mL P E I</td><td> 52</td>
<td> Example 22</td><td> 0.5 mg/tnL GOD</td><td> 2125</td><td> 1 mg/niL P E I</td><td> 50</td>
<td> Example 23</td><td> 0.005 nig/mL GOD</td><td> 670</td><td> 1 nig/mL P E I</td><td> 44</td>
<td> Example 24</td><td> 0.5 nig/mL 0 O D/1 mg/mL PSS</td><td> 482</td><td> 1 mg/mL P E I</td><td> 45</td>
<td> Example 25</td><td> 0.05 nig/mL G O D/1 mg/mL PSS</td><td> 468</td><td> 1 mg/niL P E I</td><td> 33</td>
<td> Example 26</td><td> 1 mg/mL PSS</td><td> 130</td><td> 0.5 mg/mL G O D / 1 mg/mL P E I</td><td> 382</td>
<td> Example 27</td><td> 1 mg/niL PSS</td><td> 149</td><td> 0.05 mg/mL G O D / 1 nig/mL P E I</td><td> 185</td>
<td> Example 28</td><td> 1 mg/mL PSS</td><td> 110</td><td> 1 mg/mL P E I</td><td> 40</td>
Examples 21-28: Layering and Fixation of Proteins
The Examples 21-28 were carried out to study the applicability of the present invention for constructing films composed of proteins. The results are summarized in Table
2.
Examples 21 and 22 are given for films prepared by the conventional alternate layer-by-layer method, in which GOD enzyme was layered alternately with PEI. In these Examples there is observed a very large frequency change in each adsorption step, which corresponds to a simultaneous layering of 3 to 4 GOD layers, suggesting that the GOD was assembled in the form of multi-layered and associated molecules.
By contrast, with Examples 23 and 24 in which an admixed GOD/PSS solution was employed for the alternate layering with PEI and also with Examples 25 and 26 in which an admixed GOD/PEI solution was employed for the alternate layering with PSS, the frequency changes resulting from the GOD adsorption were found to be relatively small. At the same time, such frequency changes are significantly larger than those in Example 27 and 28 in which the alternate layering was conducted using PSS and PEL Thus, it was verified that in the films of Examples 23 through 26 GOD molecules are layered and fixed without occurrence of the association of molecules, by premixing (admixing) GOD with polymer ions.
Examples 29-34: Enzyme Reaction Using the Thin Films
Examples 29-34 are to illustrate enzyme reactions carried out by immersing the films obtained as in the abovedescribed Examples 21-27 in an aqueous solution containing glucose, POD and DA67 (a redox enzyme). As the reaction proceeded, DA67 was oxidized, resulting in an increased absorption at 665 nm. This spectral change with time is an indication of the enzyme activity. Thus, the relative enzyme activities per unit weight of the enzyme were determined for the respective cases, in which the enzyme activity of the film in Example 29 was employed as a standard. The results are given in Table 3.
TABLE 3
<td></td><td> Film employed</td><td> Relative Activity</td>
<td> Example 29</td><td> Example 21</td><td> 1.000</td>
<td> Example 30</td><td> Example 22</td><td> 0.998</td>
<td> Example 31</td><td> Example 23</td><td> 0,995</td>
<td> Example 32</td><td> Example 24</td><td> 1.958</td>
<td> Example 33</td><td> Example 25</td><td> 7.407</td>
<td> Example 34</td><td> Example 26</td><td> 7.284</td>
<td> Example 35</td><td> Example 27</td><td> 67.44</td>
In Examples 29 and 30 were used the films prepared by the conventional alternate layer-by-layer method, in which the film in Example 30 was prepared from a solution with a <sub>4n</sub> smaller GOD concentration as compared with the film in Example 29. There are observed no enhancement in the relative activity with Example 30. It is clearly indicated that the employment of an admixed solution will result in an enhancement in the enzyme activity, as seen in Examples 23 and 24 in which GOD/PSS admixed solutions were used in 45 the alternate layer-by-layer assembling with PEI and also in Examples 25 and 26 in which GOD/PEI admixed solutions were used in the alternate layer-by-layer assembling with PSS.
It was also found that GOD of a smaller concentration <sub>50</sub> admixed with the polymer ions produced a higher enzyme activity as can be seen from the comparison between Examples 31 and 32 and that between Examples 33 and 34. This fact may be reasoned that the less is the GOD proportion in the admixture, the more effectively the association of GOD molecules are suppressed and the diffusion of the 55 substrate is facilitated resulting in the enhancement in the enzyme activity. It was further noted that the admixing of the enzyme with oppositely charged polymer ions in a solution led to a higher relative activity, as can be seen from a comparison between Examples 31 and 33 and also that <sub>60</sub> between Examples 32 and 34. Thus, it was shown that admixing of an enzyme with a polymer ion which will exert a stronger interaction with the enzyme results in an increased activity due to the suppression of the association of the enzyme molecules.
<sub>65</sub> Examples 35-37
The alternate layer-by-layer assembling on quartz crystal was carried out by immersing the precoated quartz crystal
6,020,175 microbalance alternately in an admixed GOD/PEI solution ([GOD]):[PEI]=0.5 mg/ml: 1 mg/ml] and a Mont solution (0.3 mg/ml) for Example 35, and alternately in a GOD solution (0.5 mg/ml) and a Mont solutions (0.3 mg/ml) for Example 36. The resultant frequency changes are shown in FIG. 4. No film growth is observed in Example 36. This is probably because both GOD and Mont were negatively charged and no adsorption due to the electrostatic interaction occurred. By contrast, in Example 35 the oppositely charged polymer ions and GOD molecules were premixed to form an admixed solution with a positive net charge, which enabled the alternate adsorptions with the negatively charged Mont.
This example also verifies that PEI, a flexible molecule present in the admixture, allowed the alternate layering of GOD with Mont (rigid or non-flexible molecules). Measurements were also conducted, for Example 37, of UV absorption at 665 nm on the film employed in Example 35. FIG. 5 shows that a regular increase in the UV absorption is observed with time, indicating a steady layering or selfassembly of GOD molecules. The subject examples thus demonstrate that the present invention of has enabled the alternate laycr-by-laycr assembling of likely charged materials as well as a hybrid-type alternate layering of an organic material and an inorganic material.
Examples 38^11: Alternate Layer-by-layer Assembly of Plural Non-flexible Materials
In Example 38 a GOD/PEI admixture (GODO.5 mg/ml, PEL1 mg/ml) was prepared for alternate layer-by-layer assembly with Mont on the precoated quartz crystal microbalance. The resultant frequency changes are given in FIG. 6, from which it is indicated that alternate GOD layers and Mont layers are successfully formed. Hitherto it has been impossible to perform an alternate laycr-by-laycr assembling with GOD and Mont as both substances arc rigid or inflexible. According to the present invention the premixing of GOD with PEI allows the alternate laycr-by-laycr assembling of such two rigid substances in which PEI presumably serve as a glue.
In Example 39, GOD (0.5 mg/ml) and PEI (1 mg/ml) are premixed for an alternate layer-by-layer assembling with PSS on the quartz crystal microbatance. The resultant frequency changes are also given in FIG. 6, from which it is indicated that alternate GOD layers and PSS layers are successfully formed. It has hitherto been impossible to conduct an alternate layer-by-layer assembling with GOD and PSS as these substances are likely charged. The premixing of GOD with PEI possibly result in the conversion of negative charge of GOD into a positive net charge, thus allowing the alternate layer-by-layer assembling with PSS, a polyanion.
In Example 40 and Example 41, enzymatic activity of GOD was determined by immersing the film obtained in Example 38 and Example 39 respectively in solutions containing glucose, POD and DA67 and measuring absorbance at 665 nm. The results are given in FIG. 7, from which it is seen that the absorbance in creases as time lapses, demonslrating the enzymatic activity 01' GOD is effectively maintained within the film assemblies.
Example 42: Alternate Layer-by-layer Assembly Composed of Different Polymer Ions of Like Charges
In Example 42, an admixed GOD/PEI solution (GOD:0.5 mg/ml, PEL0.01 mg/ml) was prepared for an alternate layer-by-layer assembling with PEI on the quartz crystal microbalance. Πιε resultant frequency changes are given in FIG. 8, from which it is seen that the alternate GOD layers and PEI layers were successfully formed. In this example, the electric charges of the admixed solution was dominated by the negatively charged GOD as the PEI concentration was adjusted to be relatively low, thereby enabling the alternate layering with the positively charged PEI. The premixing in accordance with the present invention thus makes it possible to obtain a solution of a functional molecule having any desired net electric charge, cither positive or negative, by adjusting concentration of the functional molecule relative to that of an organic polymer ion in the solution. This leads to versatile selection of a substance or material with which the functional molecule is employed for an alternate layer-by-layer assembly.
As detailed in the above, according to the present invention functional molecules are premixed or admixed with polymer ions in a solution for an alternate layer-by-layer assembling process, thereby successfully constructing functional films composed of a variety of non-flexible functional molecules such as those which have been difficult to assemble by the conventional alternate layer-by-layer method. For example, a film composed of layers of dye molecules having a low molecular weight can be formed. It is also possible to construct, from an enzyme/polymer ion admixture, a layered-structure in which the association of the enzyme molecules are suppressed to exhibit an increased enzyme activity. Additionally, the premixing with polymer ions makes it possible to convert the net electric charge of functional molecules, thereby enabling an alternate layerby-layer assembling with a substance having the same electrical charge as the functional molecules, such alternate layering being intrinsically impossible by the conventional method. Furthermore, according to the present invention there can be obtained an alternate layer-by-layer assembly made up of two or more different types of rigid molecules in a film, by the premixing with flexible polymer ions, such assembly having been impossible to obtain by the conventional method. The films of the present invention are composed of a layered-structure of a variety of functional molecules ranging from low molecular weight molecules to polymer molecules, providing good prospects of developing such devices as molecular devices and artificial reactors of the new generation.
What is claimed is:
1. A method for producing a multiple layered functional thin film which comprises:
immersing a solid support having an electric charge in a solution containing a mixture of functional molecules that provide a desired function in a physical or chemical process and charged polymer molecules, different from the functional molecules, that form a matrix to fix the functional molecules, which solution of functional molecules and charged polymer molecules having a net electric charge opposite to that of the solid support, to form a layer containing said functional molecules and said charged polymer molecules;
immersing the solid support and said layer containing said functional molecules and said charged polymer molecules in a solution containing charged polymer molecules having a net electric charge opposite to that of said solution containing the mixture of charged polymer molecules and functional molecules; and repeating at least once said steps of immersing said solid support in a solution containing a mixture of charged polymer molecules and functional molecules and in a solution containing charged polymer molecules to form a desired multi-layered thin film.
6,020,175
2. The method of claim 1, wherein the charged polymer molecules used in said solution containing a mixture of charged polymer molecules and functional molecules and the charged polymer molecules used in said solution containing charged polymer molecules are different charged polymer molecules having opposite electric charges.
3. The method of claim 1, wherein the charged polymer molecules used in said solution containing a mixture of charged polymer molecules and functional molecules and the charged polymer molecules used in said solution containing charged polymer molecules are charged polymer molecules having the same electric charge.
4. A multiple layered functional thin film produced by the method of claim 1.
5. The multiple layered functional thin film of claim 4, wherein the functional molecules are proteins.
6. The multiple layered functional thin film of claim 5, wherein the protein is selected from the group consisting of glucose oxidase, peroxidase, glucoamylase, alcohol dehydrogenase, diaporase, cytochrome, lysozyme, histone, myoglobin, and hemoglobin.
7. The multiple layered functional thin film of claim 4, wherein the functional molecules arc pigments or dyes.
8. The multiple layered functional thin film of claim 7, wherein the pigment is selected from the group consisting of mordant yellow, mordant blue, flavin adenine dinucleotide, Congo Red, tctraphenylporphinc-tctrasulfonic acid, Acid Red 27, Acid Red 26, Acid Red 52, Bismarck Brown, indigo carmine, and Ponceau.
9. The multiple layered functional thin film of claim 4, wherein as the charged polymer molecules are employed two different charged polymer molecules having opposite electrical charges.
10. The multiple layered functional thin film of claim 4, wherein the charged polymer molecules used in at least one of the solution containing charged polymer molecules and functional molecules and the solution containing charged polymer molecules are anionic polymer ions which include a functional group selected from the group consisting of sulfonates, sulfates, and carboxylates.
11. The multiple layered functional thin film of claim 4, wherein the charged polymer molecules used in at least one of the solution containing charged polymer molecules and functional molecules and the solution containing charged polymer molecules are cationic polymer ions having a functional group selected from the group consisting of quaternary ammonium ions and amines.
12. The multiple layered functional thin film of claim 4, wherein the charged polymer molecules are soluble in one of water and a water-organic solvent mixture.
13. A method for producing a multiple layered functional thin film which comprises:
immersing a solid support having an electric charge in a solution containing charged polymer molecules having a net electric charge opposite to that of the solid support to form a layer containing said charged polymer molecules;
immersing the solid support and said layer containing said charged polymer molecules in a solution containing a mixture of functional molecules that provide a desired function in a physical or chemical process and charged polymer molecules, different from the functional molecules, that form a matrix to fix the functional molecules, which solution of functional molecules and charged polymer molecules having a net electric charge opposite to that of the solution containing the charged polymer molecules;
repeating at least once said steps of immersing of said solid support in a solution containing charged polymer molecules and in a solution containing a mixture of charged polymer molecules and functional molecules to form a desired multi-layered thin film.
14. The method of claim 13, wherein the charged polymer molecules used in said solution containing a mixture of charged polymer molecules and functional molecules and the charged polymer molecules used in said solution contaming charged polymer molecules are different charged polymer molecules having opposite electric charges.
15. The method of claim 13, wherein the charged polymer molecules used in said solution containing a mixture of charged polymer molecules and functional molecules and the charged polymer molecules used in said solution containing charged polymer molecules arc charged polymer molecules having the same electric charge.
16. A multiple layered functional thin film produced by the method of claim 13.
17. The multiple layered functional thin film of claim 16, wherein the functional molecules are proteins.
18. The multiple layered functional thin film of claim 17, wherein the protein is selected from the group consisting of glucose oxidase, peroxidase, glucoamylasc, alcohol dehydrogenase, diaphorase, cytochrome, lysozyme, histone, myoglobin, and hemoglobin.
19. The multiple layered functional thin film of claim 16, wherein the functional molecules are pigments or dyes.
20. The multiple layered functional thin film of claim 19, wherein the pigment is selected from the group consisting of mordant yellow, mordant blue, flavin adenine dinucleotide, Congo Red, tetraphenylporphine-tetrasulfonic acid, Acid Red 27, Acid Red 26, Acid Red 52, Bismarck Brown, indigo carmine, and Ponceau.
21. The multiple layered functional thin film of claim 16, wherein as the charged polymer molecules are employed two different charged polymer molecules having opposite electrical charges.
22. The multiple layered functional thin film of claim 16, wherein the charged polymer molecules used in at least one of the solution containing charged polymer molecules and functional molecules and the solution containing charged polymer molecules are anionic polymer ions which include a functional group selected from the group consisting of sulfonates, sulfates, and carboxylates.
23. The multiple layered functional thin film of claim 16, wherein the charged polymer molecules used in at least one of the solution containing charged polymer molecules and functional molecules and the solution containing charged polymer molecules are cationic polymer ions having a functional group selected from the group consisting of quaternary ammonium ions and amines.
24. The multiple layered functional thin film of claim 16, wherein the charged polymer molecules are soluble in one of water and a water-organic solvent mixture.
*****
XP-002414900
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Biomacromolecules 2W4, 5, 1667-1670
1667
Multilayer Biomimetics: Reversible Covalent Stabilization of a Nanostructured Biofilm
Bingyun Li and Donald T. Haynie*
Biomedical Engineering and Physics, Instilute for Micromanufacturing, Louisiana Tech University, PO Box 10137, Ruston, Louisiana 71272
Received July 3, 2004; Revised Manuscript Received July 19, 2004
Designed polypeptides and electrostatic layer-by-layer sell-assembly form the basis of promising research in bionanoiechnology and medicine on development of polyelectrolyte multilayer films (PEMs). We show that PEMs can be formed from oppositely charged 32rners containing several cysteine residues. The polypeptides in PEMs become cross-linked under mild oxidizing conditions. This mimicking of disulfide (S—S) bond stabilization of folded protein structure confers on the PEMs a marked increase in resistance to film disassembly at acidic pH. The reversibility of S-S bond stabilization of PEMs presents further advantages for controlling physical properties of films, coatings, and other applications involving PEMs.
Introduction
PEMs are of broad and growing interest 10 scientific research in areas ranging from electronics to biomaterials.<sup>1</sup>.<sup>2 </sup>Layers of nanometer-scale thickness can be readily fabricated by electrostatic layer-by-layer self-assembly (LbL).’ the variation on the general theme when the linear charge density of the self-assembling polyelectrolytes is high (~0.5-l electronic charges per monomer). The simplicity and universality of LbL holds much promise for commercial exploitation of PEMs. Common polymers in LbL are organic homopolyelectrolytes of high water solubility but low biocompatibility. Our work in bionanoiechnology has aimed to broaden the frontier of PEMs research by initiating and developing the use of designed polypeptides for LbL.
Analysis of PEM properties has been largely concerned with chemical, mechanical, or thermal stress.'“.*<sup>1</sup>’ PEMs show reduced structural integrity or tend to dissolve*‘*'<sup>1</sup> at a pH near the pK<sub>a</sub> of the ionizable groups of the polycations or polyanions, owing to electrostatic repulsion. In the present work, we have assessed the structural integrity of polypeptide PEMs in a model harsh environment, viz. strongly acidic pH. in the presence and absence of S—S cross-links. Harsh conditions are common in industrial chemistry: they are also pertinent to some situations in biology.
There are two main ways of stabilizing a PEM: choosing polyelectrolytes of high intrinsic structural integrity and cross-linking the polyelectrolytes following assembly. As to the latter various approaches are known: thermal/photoinduced cross-linking, for instance by diazonium groups; glutaraldehyde cross-linking; other; but the modification process will be irreversible or involve a toxic chemical or structure-damaging ultra-violet radiation. The present work is concerned with cross-linking and stabilization of polypeptide PEMs by formation of S—S bonds. The approach is * To whom correspondence should be addressed. E-mail: haynie© coes.latech.edu. Phone: +1-318-257-.1790. Fax: +1-318-257-5104.
attractive for a host of reasons: polypeptides and proteins are important to biology and medicine, S—S bonds can be formed under relatively mild conditions, the number and distribution of S—S bonds can be controlled in a variety of ways, and S—S bond formation is reversible.
Development of films and coalings in food science, pharmaceutics, waste disposal, and other areas has involved proteins to a substantial extent.<sup>5</sup> This pertains to the present work because a protein comprises one or more polypeptide chains. Al the same time, however, the present work is far more general in scope, because all the different protein sequences on Earth are but a very tiny fraction of all of the polypeptide sequences that are both possible and realizable by molecular biology or synthetic chemistry.
A key amino acid in the present work is cysteine (Cys), which can form an S—S bond in an oxidizing environment. S—S bonds occur naturally in biological matter, where they are important for stabilizing folded structure of proteins, e.g. lysozyme.<sup>6</sup> To the best of our knowledge, this report is the first one in the scientific literature where PEMs of any sort are strengthened by mimicking S—S bond stabilization of proteins and, moreover, where PEMs have been fabricated from such short polyelectrolytes. The results suggest a multitude of new possibilities for developing polypeptide PEMs. Areas of research and development most likely to be affected by this work are biotechnology and medicine. Applications of this technology include implanted device coatings, drug delivery systems, and artificial cells.
Materials and Methods
Polypeptides. The sequences were (1) KVKG/KCKV/KVKG/KCKV/KVKG/KCKV/
KVKG/KCKY (2) EVEG/ECEV/EVEG/ECEV/EVEG/ECEV/
EVEG/ECEY
10.1021/bm0496155 CCC: $27.50 © 2004 American Chemical Society
Published on Web 05/06/2004
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1668 Biomacromolecules, Vol. 5, No. 5, 2004 where K. E. V. G. C. and Y represent, respectively, the amino acids lysine, glutamic acid, valine, glycine, cysteine, and tyrosine. Peptide synthesis was by F-moc chemistry. The products were confirmed by mass spectrometry and analyzed by high-performance liquid chromatography and used without further purification.
LbL Assembly and Disassembly. Peptide multilayers were assembled at room temperature on quartz crystal microbalance (QCM) resonators (Sanwa Tsusho Co., Ltd. Japan) or quartz microscope slides as described previously.<sup>7 </sup>The peptide concentration was 2 mg/mL in each case, and the buffer was IO mM tris-HCl. pH 7.4. The rinsing solution was 10 mM tris-HCl, pH 7.4. Following polyelectrolyte adsorption, each sample was dried using a stream ol dry gas. nitrogen for non-oxidized samples and air for oxidized ones. The film fabrication process was (I) prepare solutions of peptides as described above: (2) sequentially immerse the QCM resonator in each of these solutions lor 20 min: (3) rinse the resonator for several seconds alter each adsorption step: (4) dry the resonator in a stream of gas: (5) monitor the deposition of material by QCM. An illustration of him assembly is provided in the Supporting Information. QCM resonator frequency shift, Δ/’. was converted to mass of adsorbed material, Ari as Δ»! (ng) —0.87 x Δ/(Hz) (see, for example, ref Id and citations therein).
The efficiency ofcovalent cross-linking in muhilayers was measured by determining the resonant frequency at defined time points following exposure of the film to acidic pH. Samples were exposed for a defined length of time to an oxidizing environment or a reducing environment, and then immersed in a IO mM KCI solution buffered al pH 2.0. This pH is well below the pK<sub>a</sub> of the side chains of the negatively charged peptide in aqueous solution: glutamic acid titrates at pH 4.0-4.5/ After treatment in acidic pH for 240 min, oxidized samples were or were not exposed for several hours to 50 mM tris(2-earboxyethyl)phosphine hydrochloride (TCEP) buffered al pH 2.0: TCEP is an effective sulfhydryl reducing agent in the range 1.5-9.0.<sup>9</sup> QCM was used to determine mass of the PEM at defined time points. AH samples were dried in a stream of gaseous nitrogen at each time point prior to QCM measurement to minimize the dependence on frequency of the viscoelastic properties of a PEM. An illustration of film disassembly is provided in the Supporting Information.
Determination of S—S and S—H Groups. Ellman s reagent, (5,5'-dithiobis[2-nilrobenzoic acid]. DTNB). is used in a standard method of determining reactive sulfhydryls in proteins (pH 8). It can also react with S—S linkages when one free sulfhydryl group is available for reaction (pH 10.5). The product, TNB<sup>2</sup>־. has an absorbance maximum at 412 nm. Titration of cysteinyl residues with DTNB was used to characterize the relative abundance ofS~H and S—S bonds. Detailed information on procedure can be found in ref 10. Briefly, in the present context two sets of sample films, oxidized and non-oxidized, were assembled on quartz slides. For each sample or reference, I mL of DTNB solution (50 mM sodium acetate, 2 mM DTNB in H2O. pH 8.0), prepared fresh, was added to 2 mL ot I M tris, pH 8.0 and 17 mL of H2O, mixed thoroughly, and dispensed into a UV cuvette.
Communications
Oxidized and non-oxidized PEMs on quartz slides were incubated in the resulting solution for 30 min. The slides were removed, and the absorption spectra of the solutions were measured in the range 190—I 100 nm. The pH ol the solutions was adjusted to 10.5. and the samples were immersed for another 30 min. The slides were removed and the absorbance spectra were measured and compared.
Results and Discussion
We have designed peptides (I) and (2) on the basis ol principles described elsewhere. Briefly, at the pH 01 PEM assembly all ionized side chains of a peptide were required to have the same sign and polypeptide charge per unit length was required to be above 0.5 in solution, assuming complete isnization for the sake of simplicity: quantitative determination of a probable shift in side chain p/Q on PEM formation was beyond the scope ol the present study. The sequence designs were intended to test whether S-S bonds could stabilize polypeptide PEMs in a manner resembling S-S bond stabilization of ordered structure of a protein nt acidic pH.<sup>6</sup> Sequences resembling peptides (I) and (,2) but encoded by a genome could be especially useful for maximizing ' biocompatibilily or minimizing immunogenicity 01 a film, coating, or microcttpsule in the respective organism.
We have shown that peptides (I) and (2) can be used to fabricate chemically cross-linked polypeptide PEMs. The peptides were dissolved in 10 mM Tris-HCl. pH 7.4 to a final concentration of 2 mg/mL. Figure la displays film assembly on QCM resonators as monitored by QCM. The change in polypeptide mass deposited per adsorption step was linear. This implies that the surface density of charge of the substrate reversed sign on peptide adsorption, consistent with the assumed net charge at neutral pH based on amino acid sequence composition. It is remarkable that such a large quantity of designed 32mers was deposited, over 285 ng per layer; the adsorption of poly-L-lysine and poly-Lglutamic acid, which is qualitatively different, is discussed in ref 7. The behavior of the designed peptides may reflect the relative importance of hydrophobic interactions in polypeptide PEM assembly.
We have developed a novel way of ״sing QCM to measure the effectiveness of cross-linking in polypeptide PEMs. Following assembly, PEMs of peptides (1) and (2) were exposed for several hours to an oxidizing aqueous environment (air-drying for 30 min. then immersion in 20 v/v % DMSO, 10 mM Tris-HCl saturated with air, pH 7.5) or a reducing environment. Figure 1 b shows that acidic pH treatment of non-oxidized polypeptide PEMs led to film disassembly with relatively rapid kinetics. The absolute net charge of the negative polymers declined on protonation, and the positive polymers repelled each other, weakening attraction between layers. By contrast, oxidized polypeptide PEMs containing Cys retained most of their mass after 240 min at acidic pH. (Optimization of the extent of mass retention will be discussed elsewhere.) All retained material was lost from the oxidized PEMs, however, on immersion of the sample in a reducing aqueous environment: TCEP reduced S—S bonds in the oxidized PEMs, leading to complete film
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Communications
Biomacromolecules, Vol. 5, No. 5, 2004 1669
<img file="IL190885A_D0044.tif" />
<img file="IL190885A_D0045.tif" />
s? 100 in g ao « 60 ra E «0 a> .2 20
גס a> 0 a:
□ 60 120180240300360420480540
Adsorption step
<img file="IL190885A_D0046.tif" />
<img file="IL190885A_D0047.tif" />
Figure 3. Effect 01 S-S bond formation on Cys-containlng polypeptide PEM stability under extreme conditions, in this case strong acid. The cross-linked polymers would also be stable in different harsh conditions, e.g. an organic solvent. S-S cross-links stabilize the oxidized film. The formation of S-S bonds is reversible. On addition of a reducing agent, the disullide-bonded PEM becomes unstable at acidic pH. Counterions are omitted for clarity.
Desorption time, min
Figure 1. Polypeptide PEM assembly and disassembly monitored by OCM. Symbols indicate the average of three independent trials, (a) LbL ol designed 32mers 1 and 2. Deposited polymer increases linearly with adsorption step. The mass sensitivity constant for conversion 01 Irequency shift into mass deposited was assumed to be 1.B3 x 10® Hz cm<sup>2</sup> g<sup>1</sup>.’־® (b) Representative time course of loss of polypeptide from QCM resonator at acidic pH. Substantially less material was lost from S-S bonded PEMs (oxidized) than ones stabilized by van der Waals interactions alone (reduced). After treatment with a reducing agenl at acidic pH, however, complete disassembly of the Rim was observed; S—S bond formation in polypeptide PEMs was reversible.
<img file="IL190885A_D0048.tif" />
Wavelength, nm
Figure 2. Confirmation of S-S bond formation in polypeptide PEMs. S-H and S-S determination using Ellman’s reagent. Absorption spectra of non-oxldlzsd samples are shown with dashed lines, oxidized samples with solid lines. The proportion of S-S is much higher in the oxidized sample than the non-oxldlzed one, and vice versa lor S-H.
disassembly al acidic pH, as in the reduced sample. This resembles the known reversibility of S—S bond formation in proteins.״
DTNB was used to demonstrate the formation of S—S bonds in oxidized polypeptide PEMs. At pH 8, free S—H reacts with DTNB. giving a mixed disulfide and 2-nitro-5thiobenzoic acid (TNB<sup>2</sup>־). Figure 2 shows that at pH 8 (S—H determination) TNB<sup>2</sup>־ absorbance was higher in the nonoxidized film than the oxidized one, indicating more S-H groups in the former than the latter. At pH 10.5 (S—S determination), DTNB also reacts with S—S in the presence of S—H. In this case, TNB<sup>2</sup>־ absorbance was higher in the oxidized sample than the non-oxidized one: there were more S—S bonds in the former than the latter. The data thus indicate that more S—S bonds were present in samples after than before oxidation. Quantitative determination of S—S bonds per unit mass of PEM. though possible, was beyond the scope of the present work, as the primary concern was demonstration of proof of principle.
The mechanism proposed for the results of this work is presented in Figure 3. Exposure of a Cys-containing PEM to an oxidizing solution promotes S-S bond formation; cross-links form between like-charged polypeptides within a single layer and between oppositely charged polypeptides in adjacent layers. The product is a cross-linked PEM of three-dimensional structure which resists disintegration in a harsh environment, in the present case acidic pH. By contrast, non-crosslinked (“reduced) samples readily disintegrate at acidic pH, due in large measure to charge repulsion between positively charged polypeptides. S—S cross-link formation increases PEM stability against chemical degradation, subsiantially reducing the kinetics and extent of disintegration of oxidized Cys-containing polypeptide PEMs relative to non-oxidized ones (cf Figure lb).
Taken together, the experimental results indicate that oxidation of a PEM assembled from a Cys-containing polypeptides increases film stability by the following reaclion:
OXIDIZING ־נ״ן!
* ” ־ COO'-yH-CHj-SH + HS-CHy-CH-COO
NH)* REDUCING
NH,.
2H + ־ CH-CHr-S-S-CHj-CH-COO- ־COO *(NH
Other researchers have cross-linked PEMs by thermal or photoinduced processes for various purposes, e.g., micropattern polymer films, stabilize enzyme crystals for synthetic applications, enhance ion-transport selectivity of polyelectrolyte membranes, and stabilize biocompatible albumin/
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1670 Biomacromolecules, Vol. 5, No. 5, 2004
Communications heparin comings.<sup>12</sup> In till such cases, however, cross-linking was irreversible. S-S cross-linking 01' polypeptide PEMs is both distinctive and advantageous lor fabrication, it can be achieved under mild reaction conditions, for example חס air oxidation in the absence 01' added chemicals, and advantageons for controlling properties 01' PEMs. it is chemically reversible. The PEM fabrication methodology outlined in this work thus is promising for development of biocompmible coalings for implanted devices, edible food coalings.<sup>1</sup>’<sup>11 </sup>artificial cells intended for use in vivo.<sup>1</sup>’<sup>1</sup>’ and other tipplicalions.
Conclusion
Short custom-designed polypeptides (32nters) can be used to create PEMs by electrostatic LbL. Polypeptide PEMs have exceptional potential for functional design and a vast range of possible uses ווו areas involving protein-based films, coatings, und microcapsules. for example pharmaceutical science, biotechnology, food science, and waste disposal. Inclusion of Cys in a polypeptide suitable for electrostatic LbL permits controlled and reversible cross-linking between polypeptide chains under mild conditions. Stability of polypeptide PEMs to disintegration at acidic pH is subsiantially increased on film oxidation. Further investigation is needed to determine whether S—S cross-linking will stabilize polypeptide PEMs in other types of harsh environment and the extent to which the character and extent of cross-linking can be optimized for a specific application.
Acknowledgment. We thank Nikhil Pargaonkar lor assistance and anonymous reviewers for helpful comments. This work was supported by a seed grant from the Center for Entrepreneurship and Information Technology, an enhancement grant from the Louisiana Space Consortium (Louisiana NASA EPSC0R. project R127172). and the 2002 Capital Outlay Act 23 of the State of Louisiana (Governor’s Biotechnology Initiative).
Supporting Information Available. Illustrations of film assembly and disassembly. This material is available free of charge via the Internet at http://pubs.acs.org.
References and Notes (1) (a) tickle. M.: Decher. Ci. N״״״ I.,11. 2001. I. 45. (b) Zheng. Η. I*.: Lee. I.: Rubner. M. F.: Hammnnd. P. T. Adr. Muter. 2002. /4. 569. (c) Rtnailc. Η. H.: SchleiiolT. J. IJ. J. Am. Chem. Sue. 20115. /25. 6602. (d) Lvov. ׳וי. Pnneln Architecture: Interlacing Maleeidur Assemblies <m<l Immuhilizmitm Tcchmilngy: Marcel Dekker: Neu׳ York. 20110. (c) Decher. C>.: SehlenolT. J. B. Multilayer Thin Films. Wilev-VCH: Weinheim. Germany. 2003.
(2) (a) Shiani. V. A.: Koktysh. D. S.:Yun. 13. G.: Mans. R. I-.: Pappus. T. C.: Motnmedi. M.: Thomas. S. N.: Kotov. N. A. Ntrnti Lett. 2003. .1. 1177. (b) Decher. G.: Lein. 13.: Lowaek. K.: Lvov. Y.: Schmitt. .1. Bmsemmrs Bmelectrmi. 1994. 9. 677. (c) Mnltwald. H.: Lichtenfeld. H.: Moya. S.: Voigt. A.: Biiumlcr. H.: Sukhorukov. Ci.: Cantso. F.: Donath. E. Muermnal. Svmp. 1999. 14.1. 75.
(3) (a) Decher. Ci. Science 1997. 277. 1232. (b) Tripathy. S. K.: Kumar.
J. : Nnlwa. H. S. Hmidlmak t!f Pulyelectrulyte-ltiiseil Fliin Films fur Electrmiie mid Plummic Applieuihms: American Scientific Publishers: Stevenson Randi. CA. 2002: Vol. I. p I. (c) Caruso. F.: Mfthwald. H. J. Am. Chem. Sue. 1999. /2/. 6039. (d) Lvov. Y.: Caruso. F. Anul. Chem. 2001. 7.1. 4212.
(4) (a) Mao. G.: Tsao. Y. H.: Tit-relI. M.: Davis. Η. T. L״״g״1״/r 1995. 11.942. (b) Gao. D. Y.: Leporatii. S.: Moya. S.: Donath E.: Mohwnld. H. Langmuir 2001. 17. 3491. (c) Kharlampieva. E.: Sukhishviti. S. A. Lmigmiiir 2003. 19. 1235. (d) Blodgett. K. B. Phys. Beu. 1935. .5.5. 391.
(5) Gennadios. A. Prmeitubasetl Films and Cumings: CRC Press: Boca Raton. FL. 2002: p I.
(6) (a) Cooper. A.: Eyles. S. 3.: Radford. S.: Dobsoil. C. M. J. Mui. Biul. 1992, 22,5.939. (b) Morozova. L. A.: Haynie. D. T.: Arico-Muendel. C.: Van Dae). H.: Dobson. C. M. Nut. Struct. Biul. 1995. 2. S7I. (c) Morozova-Roche. L. A.: Arico-Muendel. C.: Hnynie. D. T.: Emelyanenko. V.: Van Dael. H.: Dobson, C. M. J. Mui. Biul. 1997. 268. 903.
(7) Haynie. D. T.: Balkundi. S.: Palulh. N.: Chakravanhula. K.: Dave.
K. Langmuir 2004. 20. 4540.
(8) (0) Creighton. T. E. Pnneins: Structures unit Muleenhtr Prupenies. 2nd ed.: Freeman: New York. 1993*. p 6. (b) Mendelsohn. J. D.: Barrett. C. 3.: Chon. A. J.: Moyes. A. M.: Rubner. M. F. Langnmir 2000. 16. 5017. (c) Boulmedais, F.: Bozonnet. M.: Schwinte. P.: Voegel. J. C.: Schaaf. P. Langnmir 2003. 19. 9873. (d) Zhi. Z. L.: Haynie. D. T. submitted.
(9) Han. J. C.: Han, G. Y. Anal. Biuchem. 1994. 220. 5.
(10) Robyt. J. F.; White. B. J. Biuehemitul Technlipies: Theury mid Pritciiee', Waveland Press: Prospect Heights. IL. 1990: p 237.
(11) (a) Zlieng, B.: Haynie. D. T.: Zhong. H.: Sabnis. K.: Surpuriya. V. J. Biummer. Sei. Pttlym. Ed., in press.
(12) (a) Stair. J. L.; Harris. J. J.: Bntening. M. 1-. Chem. Muter. 2001. IS. 2641. (b) Park. Μ. K.: Xia. C. J.: Advincula. R. C.: Schutz P.: Cantso, F. Langmuir 2001. 17. 7670. (c) Yang. S. Y.: Rubner. M. F. J. Am. Chem. Sue. 2002. 124. 2100. (d) Singh. A.: Santos. J. P.: Stanish. I.: Lee. Y. w. Abstr. Papers Am. Client. Sac. 2002. 223. U429. (e) Brynda. E.; Houska. M. J. Callaid tmerfuee Sei. 1996. 18.1. 18.
(13) (a) Rudra, J. S.: Haynie, D. T. submitted, (b) Haynie. D. T.: Liu. Y.: Li. B.; Palath, N. Manuscript in preparation.
BM0496I55
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(19) World Intellectual Property Organization
International Bureau (43) International Publication Date
March 2002 (07.03.2002) llllllllilllllllllllHIli (10) International Publication Number
WO 02/17888 A2
PCT (12) INTERNATIONAL APPLICATION PUBLISHED UNDER THE PATENT COOPERATION TREATY (PCT)
WO 02/17888 A2 ΙΙΙΙΙΙΙ.ΙΙΙΙΙΙΙΙΙΙΙΙΙΙΙΙΙΙΙΙΙΙΙΝΙΙΙΙΙ.ΙΙΙΙΙΗ (51) International Patent Classification<sup>7</sup>: A61K 9/52,
B01J 13/02 (21) International Application Number: PCT/EP01/09908 (22) International Filing Date: 28 August 2001 (28.08.2001) (25) Filing Language: English (26) Publication Language: English (30) Priority Data:
00118615.4 28 August 2000 (28.08.2000) EP
01112600.0 23 May 2001 (23.05.2001) EP (71) Applicant (for all designated States except US). MAXPLANCK-GESELLSCHAFT ZUR FORDERUNG DER WISSENSCHAFTEN E.V. [DE/DE|; Hofgartenstrasse 8, -80539 MUnchen (DE).
(72) Inventors; and (75) Inventors/Applicants (for US only): ANTIPOV, Alexei [RU/DE]; In der Feldmark 7, 14476 Golm (DE). VIEIRA, Euridice [PT/DE]; c/0 Max-Planck-Institut ftir Koiloid-und Grenzflfich, enforschung, 14424 Potsdam (DE). IBARZ, Gemma [ES/DE]; c/0 Max-Planck-lnstitut filr Kolloid-und Grcnzflach, enforschung, 14424 Potsdam (DE). SUKHORUKOV, Gleb [RU/DE]; Feuerbachstrasse 35, 14471 Potsdam (DE). DAHNE, Lars [DE/DE]; Stillerzeile 3, 12587 Berlin (DE). GAO, Changyou [CN/DE]; Am Muhlenberg 2, 14476 Golm (DE). DONATH, Edwin [DE/DE]; Dreetzer Strasse 1, 16845 Gicscnhorst (DE). M0HWALD, Helmuth [DE/DE]; Dr.-Gcbaucr-Strassc 21, 55411 Bingen (DE).
(74) Agent: WE1CKMANN & WE1CKMANN; Postfach 860 820, 81635 MUnchen (DE).
(81) Designated States (national): CA, JP, US.
(84) Designated States (regional): European patent (AT, BE, CH, CY, DE, DK, ES, FI, FR, GB, GR, IE, IT, LU, MC, NL, PT, SE, TR).
Declaration under Rule 4.17:
— as to the applicant's entitlement to claim the priority of the earlier application (Rule 4.17(iii)) for all designations
Published:
— without international search report and to be republished upon receipt of that report
For two-letter codes and other abbreviations, refer to the Guidance Notes on Codes and A bbreviations appearing at the beginning of each regular issue of the PCT Gazette.
(54) Title: CONTROLLED AND SUSTAINED RELEASE PROPERTIES OF POLYELECTROLYTE MULTILAYER CAPSULES (57) Abstract: Method of layer-by-layer (LbL) assembly of oppositely charged polyelectrolytes was applied to coat fluorescein particles. These particles with a size of 4-9 pm were prepared by precipitation of fluorescein at pH 2. Polysterensulfonate (PSS) and polyallylaminc (PAH) were used to compose the polyelcctrolyte shell on the fluorescein core. The release of fluorescein molecules through the polyclectrolytc shell core dissolution was monitored at pH 8 by increasing fluorescence intensity. The number of polyelectrolyte layers sufficient to sustain fluorescence release was found to be 8-10. Sequentially adsorbed layers prolong core dissolution time for minutes. The permeability of polyelectrolyte multilayers of the thickness of 20 nm is about 10’<sup>8</sup> m/s. Mechanism of fluorescence diffusion and osmotically supported release is under discussion. The features of release profile and possible applications of LbL method for shell formation in order to control release properties for entrapped materials are outlined. Also ambient conditions of pH, temperature and salt concentration were changed to control the permeability of polyelectrolyte multilayer capsules.
WO 02/17888
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Controlled and sustained release properties of polyelectrolyte multilayer capsules
Description
The present invention relates to methods of controlling the permeability of micro containers for drug encapsulation and release, and especially the control of sustained release properties of polyelectrolyte multilayer capsules.
A major task in the development of advanced drug formulations deals with the elaboration of delivering systems providing sustained release of bioactive materials. Mostly, these delivering systems comprise polymer particles in the size range of 10<sup>2</sup> to 10<sup>5</sup> nm. The drug molecules are embedded in polymer matrices or in core-shell structures. In the latter the shell degradation rate determines the release rate of the bioactive core material.
In principle, a shell around the active core can be fabricated by adsorption of polymers or biopolymers onto the drug' particle surface [1] or by adsorption of the monomers with subsequent polymerization at the interface [2-4]. The composition of the shell may additionally provide certain functionalities. It may be adjusted to facilitate the interaction of the core with the solvent or to add certain desired chemical properties. The shell may also have magnetic, optical, conductive, or targeting properties for directing and manipulating the core containing bioactive material.
Recently, a novel type of shell structures constituting polymer capsules has been introduced [5-7]. These novel hollow polymeric capsules have a predetermined size in the sub-micron and micron range and tunable wall properties [7,13-15]. These capsules are fabricated by means of layer-by
WO 02/17888 layer (LbL) assembling of polyelectrolytes onto colloidal particles with subsequent removal of the colloidal core. The layer-by-layer (LbL) assembling is performed by alternating adsorption of oppositely charged species, such as polyelectrolytes [16,1] onto the surface of colloidal particles. The driving fcv-se for LbL adsorption is the electrostatic attraction between the incoming polymer and the surface.
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Various cores, e.g. organic or inorganic materials, biological cells, drug crystals or emulsion droplets, ranging in size from about 60 nm to tens of microns have been utilized as templates for multilayer formation by the LbL technique. Up to now a variety of different substances, such as synthetic and natural polyelectrolytes, biopolymers, proteins, nucleic acids, magnetic and fluorescent inorganic nanoparticles, lipids, etc. were employed as layer constituents to build the multilayer shell on colloidal particles. The thickness of the shell walls depends on the conditions of its preparation. It can be tuned in the nanometer range. The thickness of the multilayer films on colloidal particles can be adjusted in the nanometer range e.g. by adsorption of varying numbers of layers. It was established [8, 9] that the capsule walls have semipermeable properties. They are permeable for small molecules such as dyes and ions while they exclude compounds with a higher molecular weight [17,9].
There is a variety of materials, the encapsulation of which is desirable for application in different areas of technology, such as catalysis, cosmetics, medicine, biotechnology, nutrition and others.
One possible approach to load capsules with polymers is to embed the desired polymers within the inner layers of the shell structure while forming the capsules and to desorb polyelectrolytes, e.g. multivalent ions, from inner layers of empty shells into their interior [18]. Extraction of these ions results then in the release of the polymers into the capsule interior.
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Another approach is to directly synthesize polymers inside the capsules by taking advantage of the permselectivity of the capsule walls [19]. While capsules can be successfully loaded thereby these methods have only limited applicability with regard to the polymer species and often harsh conditions have to used for core dissolution or polymerization, being e.g. a low pH, oxidizing agents or organic solvents, which are used for core decomposition, or an elevated temperature during synthesis.
It would be desirable to provide systems having controllable or adjustable loading as well as release properties. In particular a method would be favourable which allows the loading or release of materials into and from capsules by modifying the capsule wall permeability. Further, for most applications a defined and controllable permeability of the capsule wall is required in order to control the process of loading the capsules as well as any subsequent release under specific environmental conditions. Due to the fact that the loading is preferably fast, but the release should be in most applications slow, it is further desired that the permeability is switchable.
It was therefore an object of the present invention to provide methods to influence, vary or switch properties of capsule walls. Another object of the invention was to provide means to introduce macromolecules into the capsules and to switch and control capsule.permeability for them.
These objects are solved by a process for controlling the permeability of polyelectrolyte multilayer capsules by variation of the reaction conditions during the preparation or use of the capsules, characterized in that at least one of the reaction conditions of pH, temperature, salt concentration, ion composition, ion concentration, ionic strength, solvent composition or solvent concentration is varied.
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The invention further relates to a process for controlling the permeability of polyelectrolyte multilayer capsules, wherein the number of polyelectrolyte layers is adjusted in such a way that the desired permeability is achieved.
According to the invention the permeability of polyelectrolyte multilayer capsules can be determined, varied or/and controlled by parameters of the environment of the capsules, e.g. reaction conditions during preparation or use of the capsules, media, in which the capsules are contained or into which the capsules are transported. It was found that the permeability to high molecular weight compounds as well as low molecular weight compounds can be adjusted according to the needs in different applications.
As used herein high molecular weight compounds or macromolecules are molecules having a molecular weight of at least 30 000 Da, more preferably at least 50 000 Da and most preferably at least 70 000 Da. Low molecular weight compounds or small molecules are molecules having a molecular weight of less than 10 000 Da, preferably less than 5 000 Da and more preferably less than 1 000 Da.
The permeability control according to the invention offers a unique tool for entrapping molecules within capsules and releasing them in a predetermined manner, e.g. over an extended period of time or at a i
desired, predetermined site or time point.
The process according to the invention enables particularly a reversible amendment of the permeability of capsules. This enables specifically charging the capsules with desired active substances or specifically releasing active substances entrapped in the capsules, respectively, by amending the environmental conditions of the capsules in a simple way. Thus, e.g. a permeability increase makes it possible to later charge the finished capsules with active substances. Such an open condition,
WO 02/17888 wherein active substances can permeate through the capsule walls is present according to the invention when over 50%, more preferably over 70% and most preferably over 90% of the capsules are permeable. After the capsules have been charged, e.g. during storage or transport, the permeability of the capsule wall to the entrapped active substance can be reduced by adjusting of suitable conditions so that no active substance can leave the capsules. Such a closed condition of the capsules, however, at the same time prevents that further, possibly undesired substances can enter the capsules. At the desired time and site of release, respectively, the active agent can be released in a defined way, e.g. delayed, by increasing the permeability of the capsule walls. Further, it is possible to obtain a release in certain compartments of cells or certain areas of an organism by using capsule walls exhibiting high permeability to the entrapped active substance under conditions prevailent in the desired tissue.
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According to the invention the permeability of capsule wall and thereby the incorporation or exclusion of macromolecules can be tuned by environmental conditions in a defined manner. Capsules composed of polyelectrolytes, the charge of which depends on the pH, can be used for a pH-controlled uptake and release of macromolecules.
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The practical use of polyelectrolyte capsules for sustained drug release requires quantitative data on the permeation of small molecules through polyelectrolyte walls, Which are presented herein.
In the light of sustained release it would be advantageous to be able to decrease the layer permeability for small polar molecules once they are encapsulated. One possible way to approach this goal is the use of lipids as a layer constituent [9, 10]. Herein, the formation of thicker capsule walls is presented in detail being a favourable and easy way to decrease permeation. It was found that increasing the layer number will decrease penetration of the shells by encapsulated material or molecules.
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To verify this approach fluorescein microparticles were covered with a different number of polyelectrolyte layers. Dyes like fluorescein can be considered as model substances for a large class of drugs. Afterwards core dissolution was initiated by a pH change and monitored by the increasing fluorescence in the bulk.
It was found that polyelectrolyte multilayer shells assembled around cores consisting of low molecular weight compounds provide barrier properties for release under conditions where the core is dissolved. This finding is a סו novel approach for fabrication of systems with prolongated and controlled release properties. The release can be adjusted with the number of assembled polyelectrolyte layers. The capsule permeability for low molecular weight compounds was found to depend strongly on the number of polyelectrolyte layers in the capsule.
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A large variety of synthetic polyelectrolytes with different properties, lipids, and polysaccharides have been already used for multilayer assembly [9, 12], This provides many possibilities to tune the release properties of the shells together with ensuring biocompatibility and possibility of using 20 various cores. The assembling of shells by LbL technique opens new pathways for biotechnological applications, where controlled and sustained release of a substance is required. Many problems connected with drug formulation, release, and delivery, controlling the concentration in the organism and periodicity of its reception can be solved by the formation of 25 shells on precipitates and nanocrystals. Further it is not difficult to add to the polyelectrolyte layer targeting properties. This way the affinity of polyelectrolyte multilayer coated drugs to specific or injured tissues can be increased.
In the following the release properties of capsules with regard to the number of layers forming the capsule wall are discussed in more quantitative terms using fluorescein as model substance (MW ~ 350 Da).
WO 02/17888 PCT/EP01/09908
The permeation of a molecule such as fluorescein through the shell wall is described by its permeability (P). Equation (1) combines a flux (J) with parameters of the system and the rate of change of fluorescein concentration, c<sup>e</sup>, in the bulk. When this rate is constant one may easily calculate the permeability (P) from the slope of the fluorescence increase (part 2 of Fig.3).
at (I) where V<sub>o</sub> is the volume of solution, J is the fluorescein flux through the capsule walls with the total surface area of S, and (c<sup>1</sup> - c<sup>e</sup>) is the difference of the fluorescein concentration inside (c<sup>f</sup>) and outside (c<sup>e</sup>) the capsules.
As long as a core of solid fluorescein is present within the capsules, the interior of the capsules contains a saturated fluorescein solution, c<sup>s</sup>, of 25 mg/ml. Hence, the concentration difference at the beginning of the process in the right side of Eq.1 can be safely replaced by c' = c<sup>s</sup>. The capsules were assumed spherical with an average diameter The permeability can thus be calculated from
For 8 to 18 layers the permeability value was in the order of 10'<sup>8</sup> m/s. Assuming single polyelactrolyte layer thickness of 2 nm the permeability can be converted into a diffusion coefficient (D) by means of multiplying the permeability with the shell wall thickness. The calculated diffusion coefficients are in the order of 10'<sup>15</sup>m<sup>2</sup>/s.
If the permeability of the polyelectrolyte multilayer is provided by diffusion through the entangled polymer network, it should scale with the inverse of the layer thickness. The behavior of the permeability times thickness as a function of the number of layers is shown in Figure 4. As can be seen, the
WO 02/17888 permeability decreases with increasing layer number much faster than expected from a straightforward thickness increase. Only from approximately 8 layers onwards the permeability multiplied by the shell thickness becomes a constant indicating that the permeability is now controlled by the thickness increase, for example, the diffusion limiting region is the polyelectrolyte layer. This finding is consistent with the earlier observations [11] where it was shown that the conformation of the first eight layers differs from that of further assembled layers. These deeper layers are more densed resulting in a fivefold reduction of the estimated diffusion coefficient as can be inferred in Fig. 4.
A permeability coefficient might also be calculated from the release profile at the third stage of the fluorescein release curve. It can be expected that the time dependence of the release at this stage is exponential:
/ / / <sub>p</sub>-<sub>L</sub> 3) ץ)
X / i ’ where S and V represent the surface and the volume of an average capsule. However, the permeability estimated from this equation was one order less than the one calculated from the slope of the linear region. There are currently two possible explanations for this discrepancy. Either the polydispersity of the particles contributes to an apparent prolonged release, because the characteristic time release V/SP increases linearly with the particle radius. Or, the relaxation of the osmotic stress towards the end of release may reduce the permeability.
In the following the permeation mechanism is discussed in more detail. One may distinguish between diffusion through water filled pores and a bulk diffusion mechanism through homogeneous phase of polyelectrolyte multilayer shell. For thinner walls the drastic dependence on shell thickness
WO 02/17888 may be explained either by existence of pores that are successively closed by further layer deposition or by thickness dependent diffusion coefficient. The latter was indeed observed with permeation studied by planar polyelectrolyte films where typical values of D between 10’<sup>18</sup> and 1O<sup>20</sup>־<sup></sup>m<sup>2</sup>/sec were derived [ 11 ]. In order to compare our results with those of the previous study we should remark the following differences.
- According to the method described in [11] the films were prepared by drying after each adsorption step which is not possible during particle coating and which leads to a denser film. i a §
- The measurement consisted in depositing a dye probe in a defined depth into the film and observing time dependent fluorescence changes due to quencher diffusion. For sufficiently small pore concentration, which is surely the case here, this technique is only sensitive to bulk diffusion and will not reflect the permeation through pores. '
Thus one may expect that the diffusion coefficients derived from permeability data are larger than values measured in [11]. Still, this cannot ’ explain the difference of 3-4 orders of magnitude and therefore they more j probably correspond to diffusion through pores. Comparing the diffusion coefficient D with that in bulk water (~ 1O'<sup>10</sup> m<sup>2</sup>/s) which is an upper limit for the diffusion in the pore volume we may estimate the fraction of pore volume inside the walls larger than 10‘<sup>5</sup>.
Next a possible mechanism of pore formation is adressed. A destabilization of the wall may be expected, since on increasing the pH towards 8 the aminogroups of PAH may deprotonate and this may result in pore formation within the multilayers. Another possibility of pore formation is } the osmotic pressure due to the water coming to the interior as a result of fluorescein core dissolution. The related hydrostatic pressure difference creates a tension in the wall which may widen existing or create new
WO 02/17888 pores. As seen on Fig.3 (part 1), especially for bigger numbers of layers, in the beginning of dissolution the release is sustained. It is assumed that the polyelectrolyte shell suffering osmotic pressure from inside resists release of fluorescein until the fluorescein molecules develop a path out of capsules. The pores are formed as a result of this rearrangement of polyelectrolyte multilayers. It should be noted that templates and the resulting capsules have different diameters and also heterogeneous wall thicknesses. The diffusion coefficient is thus an average but there may still be larger templates with slower release profile.
In summary, it can be noted that by increasing the number of layers of polyelectrolyte capsule walls the permeability of the capsules can be reduced. For a delayed release preferably capsules having 8, more preferably 9 and most preferably > 10 layers are used.
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In a preferred embodiment the invention relates to a novel approach for encapsulating materials and molecules, such as macromolecules, biopolymers, drugs etc., in pre-formed hollow polyelectrolyte capsules. According to this embodiment of the invention the material or/and molecules can be introduced in hollow capsules rather than forming capsules around the materials/molecules.
Th.e properties and structure of polyelectrolyte multilayers are found to be sensitive to a variety of physical and chemical conditions of the surrounding media. In particular, the pH is one of the physico-chemical parameters, which influences the state of the inter-polyelectrolyte complex [20,21], especially in the case, if the charge of one polyelectrolyte in the complex depends on the pH. The polyelectrolyte pair, poly (styrene sulfonate) (PSS) and the relatively weak polycation polyfallylamine hydrochloride) (PAH), has been most extensively used for producing multilayer films on flat and colloidal surfaces (1) and serves as exemplary
WO 02/17888 polyelectrolyte pair for illustrating the invention. However, the invention is not limited to this specific polyelectrolyte pair.
By using different polyelectrolytes, the permeability can be further modified. The combination of cationic and anionic polymers results in almost unlimited variation possibilities. Characteristic values, such as polarity and polymeric rigidity can be adjusted via the chemical composition and have a specific effect on different substance classes. For example a reduction of the polarity results in a higher hydrophobicity, which decreases the permeability for polar, water soluble substances, whereas the permeability for unpolar, oil soluble substances is enhanced.
In addition, the permeability behaviour of the capsules can be strongly modified via the molecular weight and the degree of branching of the polyelectrolytes used. The molecular weight is advantageously set between 10 000 and 500 000 g/mol, wherein generally higher molecular weights and increasing branching lead to higher capsule stability and lower permeability.
By varying the pH of the medium, the permeability of the walls of microcapsules can be varied. While it is not intended to be bound to a specific mechanism of the pH-induced permeability change, it is supposed that changes of the polyelectrolyte charge upon pH variation are able to induce pore formation'(22) or loosen the polyelectrolyte network, thus enabling polymer penetration. An influence of the ion concentration going along with the pH change may also contribute to the permeability change.
This possibility of switching the capsule walls between an open and closed state provides a convenient and efficient tool to control the uptake and release of molecules, in particular polymers, biopolymers and nanoparticles. For instance, the capsules might be loaded at low pH and after increasing the pH the material is captured inside. For release the pH can be slightly
WO 02/17888 decreased again, whereby the kinetics of release can be tuned by the pH. The herein demonstrated possibility of controlling loading and release of macromolecules into and from polyelectrolyte capsules allows for widespread application. The described pH-induced permeability change of the polyelectrolyte network in the film is a general mechanism for modifying the permeability of polyelectrolyte multilayers and is not limited to a specific composition of the shell. Investigations on flat polyelectrolyte films made from weak polyelectrolytes have shown that pores can be created by changing the pH or the salt concentration.
We have found that permeability of capsules composed of polyelectrolytes, in particular of weak polyelectrolytes, strongly depends on the pH. Being impermeable for macromolecules at a pH when the charges of two polyelectrolytes forming the capsule wall are compensated, capsules are open at a pH, at which a weak polyelectrolyte is completely charged. This dependence gives an opportunity to encapsulate polymers by opening and closing a. capsule by means of pH. By means of AFM at the open state pores ranging in size from 100 to 300 nm were observed in the capsule wall. A further remarkable feature of the process of pore formation by pH variations is that the pore formation or increased permeability is reversible.
Further permeability of the capsules inversely depends on the number of layers they consist of. Employment of both these factors gives a possibility to regulate capsule release properties for low as well as for high molecular weight compounds. Fluorescein particles, stable at acidic pH can be used as core. They can be covered with different numbers of polyelectrolyte layers. The kinetics of fluorescein dissolving and release was measured at base pH. It was found that time of core decomposition depends strongly on the capsule wall thickness. During the dissolving a sustained release of fluorescein was observed.
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Permeability control by means of pH and capsule wall thickness is proposed as a new approach for controlled uptake and release of different substances into and from capsules. It opens avenues for using polyelectrolyte capsules for many applications, such as drug cariers, microreactors and so on.
In summary, it can be stated that by increasing the pH a reduced capsule permeability can be achieved and by reducing the pH an increased capsule permeability can be achieved, whereby this process is reversible. It was found that capsule walls particularly at a pH of > 8, more preferably at a pH of > 10 are impermeable (closed condition), whereas at a pH of < 6, particularly of < 4 a permeability (open condition) of the capsule walls can be achieved. The change in pH represents a simple way for adjusting the permeability and by amending the surrounding medium makes it possible to
וי ו provide for a permeability switch for the capsules. | J
This application also presents a novel, simple and very gentle method for targeted encapsulation and release of sensitive, macromolecules by controlling the capsule wall permeability by the salt concentration. Salts have an immense importance in the living organisms. The salt concentration in the cytoplasm and in the extra cellular medium is strongly regulated by the permeability of the cell membranes, by osmosis and by active transport via energy driven pumps. The physiological concentration of sodium chloride in ׳ plasma is about 0.15 M, other ions, such as potassium or calcium are crucial for signal transduction across the membrane and inside the cell.
The permeability of hollow polyelectrolyte capsules, preferably of capsules made from PAH/PSS can be reversibly switched between an open and closed state by varying the salt concentration in a narrow concentration range between 0.5 .. 2 x 10'<sup>2</sup> M/l. The increase of the salt concentration
WO 02/17888 leads to a reversible opening of the capsule wall for large molecules of MW above 50 000 Da, preferably above 70 000 Da.
The absence of pores in scanning force microscopy images, the relatively small permeability and the step-like descrease of the Forster resonance energy transfer in the wall with increasing salt concentration indicates a weakening of the electrostatic interactions between the polyelectrolytes and a subsequent swelling connected with a much better diffusion of the polymers. Salt triggered permeability is a very easy, important, and effective way for the encapsulation and release of, especially, sensitive macromolecules such as enzymes, proteins, or DNA in micro- and nanocontainers.
In summary, it can be noted that by increasing the salt concentration an increase of the permeability of the capsule walls can be achieved, whereas reducing the salt concentration causes a reduction of the permeability (closed condition). Preferably the capsule walls are made permeable by a salt concentration of at least 2 x 10’<sup>2</sup> M, more preferably of at least 3 x 10’<sup>2</sup> M and most preferably of at least 1 x 10’<sup>1</sup> M. If a closed condition of the capsules is desired, the surrounding conditions are adjusted to a salt concentration of at most 5 x 10’<sup>3</sup> M, more preferably of at most 1 x 10’<sup>3</sup> M and most preferably of at most 1 x 10’<sup>4</sup> M.
Suitable salts according to the invention are all heteropolar compounds comprising at least one anion and at least one cation. The anions and cations can be singly charged or multiply charged ions. For adjusting the permeability preferably inorganic salts are used, particularly metal salts, such as metal halogenides, particularly alkali metal halogenides. Examples of particularly preferred salts are salts containing an alkali metal cation, particularly Li<sup>+</sup>, Na<sup>+</sup>, K<sup>+</sup>, an earth alkali metal cation, particularly Mg<sup>2+</sup>, Ca<sup>2+</sup> or a different metal cation, e.g. Al<sup>3+</sup>, an iron ion, etc. and an anion, e.g. a halogenide anion, or a different anorganic anion. The metals may
WO 02/17888 also be replaced by other positively charged groups, e.g. an ammonium group׳, a sulfonium group or a phosphonium group. However, it is also possible to use organic salts, particularly salts containing organic anions.
Apart from the salt concentration, the permeability can also be adjusted by the ion concentration and ion composition of the environment, respectively, wherein also here it was detected that for higher ion concentrations a permeability is achieved, whereas for low ion concentrations an impermeable capsule wall was obtained.
The ion composition particularly plays a role, since the permeability of the capsules is influenced by interactions between ions of the surrounding medium and the charges of the polyelectrolyte shells. By suitably selecting the ions of the surrounding medium, e.g. ions forming complexes with the polyelectrolytes of the capusule shells, the permeability can be adjusted.
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The dependence of permeability on salt concentration, ion composition and ion concentration can be particularly used advantagepusly by administering encapsulated active substances to organisms, e.g. mammals and particularly humans. Therefor capsules can first be charged with active substances, wherein in vitro the capsule walls are made permeable to the active substance with the help of the above described measures. Then the encapsulated active substances can be stored in a stabil form, e.g. by adjusting a salt concentration of the storage medium to < 5 x IO<sup>3</sup>־ M. This can be done e.g. by storage in distilled, perferably in sterile distilled water. The administration of charged capsules is accompanied by an amendment of the surrounding medium, wherein, as already stated above, the physiological concentration of sodium chloride in plasma is about 0.15 M. Under these surrounding conditions the capsules are permeable to the active substance so that the active substance is released in the target tissue.
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The invention also relates to a simple method for the polyelectrolyte capsules allowing opening and closing of the wall for large polymers but also for small organic molecules and to control the permeability in a simple way by temperature treatment.
It has been shown, that the permeability of thin polyelectrolyte walls can be switched easily by heat. This is probably caused by an temporarily swelling of the wall due to stronger dissociation of the cation-anion bonds at higher temperature, followed by hydration of the formed charges and entanglement of the polymer chains. The reversibility of this process provides an excellent tool for loading hollow polyelectrolyte capsules with large macromolecules, polymers or nanoparticles for drug encapsulation as well as for the controlled and intelligent release of active substances. For example, in the agriculture many pests are active mainly at high temperatures. Encapsulation of pesticides in such capsules can ensure, a release only at hot and sunny days. Or, in the new generation of intelligent clothes, deodorants will be released only in case of strong swetting.
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Preferably at a temperature of up to 50°C, more preferably up to 40°C, the permeability is low (closed condition), whereas at a temperature of above 50°C, particularly of at least 60°C^ permeable capsules (open condition) are obtained. By increasing the temperature in a simple way a permeability increase can be achieved.
In a further embodiment of the invention the permeability of polyelectrolyte multilayer capsules is amended by varying the solvent composition or solvent concentration. Thus, the release behaviour can be adjusted via the solution, wherein as solution e.g. polar solutions, particularly water or/and polar solutions or mixtures thereof can be used. Particularly suitable solutions for adjusting the release behaviour are alcohol/water mixtures, wherein the alcohol content, e.g. methanol, ethanol or propanol, can be adapted to the individual application.
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Further, the permeability of polyelectrolyte multilayer capsules can further be influenced by adding surfactants, such as sodium dodecylsulfate (SDS) or dipalmitoyl-DL-a-phosphatidyl choline (DPPC) to the surrounding medium or as coating for the core used in capsule production.
The permeability of polyelectrolyte multilayer capsules can also be influenced by light. Photosensitive groups in the electrolyte layer, such as azo compounds or organic bisazides can be modified chemically by light, which may lead e.g. to an increase of the permeability or to a reduction of the permeability, if the photosensitve compositions are selected which cross-link by exposure to light.
As explained above, according to the invention it is possible to insert further components into the polyelectrolyte layers in order to obtain a broad modification of the permeability. The further components can e.g. b.e bound covalently to the polyelectrolyte or be independent molecules or particles, which are only embedded in the polyelectrolyte layers. The further components can be incorporated together wjth the polyelectrolyte or as independent units by using various methods, preferably the layer-bylayer method, but also a single step method or subsequent diffusion.
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The microcapsules, in particular hollow microcapsules, whose permeability can be controlled according to the invention preferably can be fabricated by alternating deposition of oppositely charged polyelectrolytes on soluble colloidal templates. The polyelectrolyte capsules can e.g. be prepared by covering templates, ranging e.g. from 60 nm, preferably from 100 nm, to 10 /2m, preferably to 2 pm in size, with alternating layers of polycations and polyanions [6,7], After formation of a polyelectrolyte wall of sufficient thickness, the templates can be dissolved and hollow capsules are obtained. The templates can e.g. be removed by changing the pH or by oxidative decomposition of the template. This is possible due to the remarkable property of the capsule wall to be permeable for small
WO 02/17888 molecules having a molecular weight of less than 10 000, preferably less than 5 000 and particularly less than 1 000 but not for polymers. The template determines size and shape of the capsule. Monodisperse capsules in the range from 500 nm to 10μνη can be prepared. Suitable capsules and their production and composition are described, e.g. in WO99/47252, WO99/47253, WOOO/03797 and WOOO/77281, the disclosure of which is herein incorporated by reference.
A remarkable feature of the capsule wall is that their properties can be tuned within wide ranges by varying the layer material and/or number or/and by varying environmental conditions such as pH, salt concentration, ion strength, ion composition, solvent concentration, solvent composition or/and temperature. These capsules offer broad perspectives in nanoscale encapsulation of drugs, enzymes, DNA, minerals, dyes, polymers, proteins and/or other active macromolecules. / .'
The capsules are preferably fabricated by alternate adsorption of oppositely charged polyelectrolytes onto the surface of colloidal particles. Different cores having a size varying from 0.06 preferably from 0.1 to 10 pm, such as inorganic colloidal particles, biological cells, protein aggregates, drug nanocrystals can be used. Hollow capsules can be produced by subsequently dissolving the core.
The permeability of Capsules is of essential interest because of its significant importance in diverse areas, relating e.g. to biotechnology, medicine, food industry, etc.
The invention shall be further illustrated by the following examples and figures:
Fig. 1: Scheme of the polyelectrolyte multilayer deposition process and of the subsequent core dissolution. The initial steps (A-D) involve stepwise
WO 02/17888 shell formation on a fluorescein core. After the desired number of polyelectrolyte layers is deposited the coated particles are exposed to pH (E) and core dissolution with fluorescein penetration into the bulk is initiated resulting finally in fully dissolved cores and remaining empty capsules (F).
Fig. 2: Fluorescence increase upon time, obtained by dissolving fluorescein particles covered with shells of different thickness (9, 13, 15, and 18 layers).
Fig. 3: Three stages of fluorescein core dissolution covered with 17 PSS/PAH layers.
Fig. 4: Fluorescein diffusion as a function of layer number. ; !
/ <sup>15</sup> / /
Fig. 5: Permeation and encapsulation of FITC-dextran (M.w. 75 000) into polyelectrolyte multilayer capsules. Left - pH = 10, center - pH = 3, right - pH increased to 10 after the capsules were loadeql with FITC-dextran at pH = 3. The bulk FITC-dextran was removed by washings at pH = 10. 20 Top - scheme, center - confocal images of the capsules, bottom fluorescence profile along the line indicated in the confocal images.
Fijg. 6: Confocal Laser Scanning Microscopy images showing: a) capsules for which the washings and the core dissolution was performed in the 25 presence of 0.05 M NaCI; b) capsules which were washed with pure water after each deposition step; 24 h incubation in a 10'<sup>3</sup> M PAH-Rho solution; c) same procedure as in b) but incubation in presence of 10’<sup>2</sup> M salt.
Fig. 7: Efficiency of the Forster Resonance Energy Transfer in capsules 30 containing the 10<sup>th</sup> layer PAH-fluo and the 12<sup>th</sup> layer PAH-rho in dependence on the salt concentration. The inset shows a typical fluorescence spectrum of these capsules. Excitation was set at 495 nm.
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Fig. 8: Time-dependent decrease of the FRET efficiency as a function of the salt concentration.
Fig. 9a): Capsules, loaded with 5 x 1O’<sup>3</sup> M PAH-rho according to the 6 protocol shown in Fig. 9b) Same capsules after release of the encapsulated PAH-rho induced by a 3 x 10‘<sup>2</sup> M salt solution.
Fig. 10: Scheme of encapsulation and release of macromolecules by switching the permeability salt concentrations changes.
Fig. 11a): CLSM image of capsules in presence of 10<sup>3</sup>־ M Fluorescein-PAH (MW 70 000 g/mol, polymer exclusion); b) CLSM image of capsules in presence of 10<sup>3</sup>־ M Rhodamine-Dextran (MW 50 000 g/mol, accumulation);
Fig. 12a): CLSM image of capsules in presence of 10’<sup>3</sup> M Rhodamin-PAH (MW 70 000 g/mol) at 23°C; b) encapsulated Rhodamine-PAH in capsules after heating the solution for 20 min to 60°C and subsequent washing with water. ; \
Fig. 13: Permeability of capsules composed of 8 layers of PSS-PAH for a labeled dextran, molecular weight 77 000 at'a low and high pH.
Fig. 14: Characteristic time of dissolving of fluorescein core, covered with different number of PSS-PAH polyelectrolyte layers.
Fig. 15: The permeation of high molecular weight molecules.
Table 1: Percentage of filled capsules in solutions of PAH-rho, 5 x 10<sup>3</sup>־ M, after 24 hours incubation time and in presence of different salt 30 concentrations.
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Examples
Example 1: Varying number of polyelectrolyte layers
Materials
Polyelectrolytes. Sodium polystyrene sulfonate) (Na-PSS, MW ~70 000), polyfallylamine hydrochloride) (PAH, MW ~50 000), and fluorescein, sodium salt, were obtained from Aldrich. Ethanol, sodium chloride, boric and hydrochloric acid were purchased from Sigma. All materials were used without further purification.
The water used in all experiments was prepared in a three stage Millipore Milli-Q. Plus 185 purification system and had a resistivity higher then 18.2 ΜΩ cm. ,
/ ׳׳ ' i Methods
Fluorescein particles were prepared by addition of one part of ethanol and four parts of hydrochloric acid, pH 2, to one part of 15 mg/ml aqueous fluorescein solution. The particle size was measured by optical microscopy. The 4-9 //m in diameter fluorescein particles, were washed in hydrochloric acid by 5 repeated centrifugation circles at 450 g. To prevent preliminary core decomposition all further multilayer deposition and washings were performed in hydrochloric acid at pH 2.
Polyelectrolyte multilayer assembly. The multilayer assembly was accomplished by adsorption of polyelectrolytes at a monomer concentration of 10<sup>2</sup>־ M in 0.5 M NaCI, pH 2. Oppositely charged polyelectrolyte species were subsequently added to the suspension of fluorescein particles followed by repeated centrifugation cycles in hydrochloric acid [7]. Fluorescein particles were allowed to interact with polyelectrolyte solution for 15 minutes. Fluorescein particles were
WO 02/17888 centrifuged at 700 g for 10 minutes. Gentle shaking followed by 1 minute ultrasonication was used to disperse particles after centrifugation.
Fluorescence spectroscopy. The core dissolving was conducted in H<sub>3</sub>BO<sub>3</sub>-NaCI-NaOH buffer, pH 8. The kinetics was followed by recording the time dependence of the emission at 522 nm. Excitation was set at 488 nm.
Confocal microscopy. Confocal images of capsules after dissolving the core were obtained by means of a Leica confocal scanning system. A 100 x oil immersion objective with a numerical aperture of 1.4 was used.
Figure 1 provides the scheme of fluorescein particles encapsulation and release. After LbL adsorption (Fig. 1A-1D) core dissolution is initiated by changing the pH from pH 2 to pH 8 (Fig. TE) and completed after a certain period of time (Fig. 1F). ί ו
Fluorescein particles rapidly dissolve at pH 8. The ipiea was thus to slow down the rate of core dissolving by covering the particles with a polyelectrolyte multilayer. Shells walls consisting of a different number of layers were fabricated and examined with’ regard to their fluorescein permeability behavior. Fluorescence spectroscopy is a convenient tool for the determination of the core dissolving rate because the fluorescence of the core is completely suppressed as a consequence of the self-quenching of the dye. Upon releasing the dye into the bulk the fluorescence intensity increases. Thus the rate of cores dissolving can be directly followed by measuring the fluorescence increase in the sample.
In Fig. 2 typical time-dependent fluorescence curves obtained by switching the pH to 8 are shown. Fluorescein particles covered by layers of different thickness (9, 13, 15, and 18 layers) are compared with the control demonstrating the dissolving of naked fluorescein particles.
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As shown in Figure 3, after a comparatively short induction period (1) the rate of dissolving becomes constant (2) before finally the fluorescence in the bulk levels off (3). The initially more slowly increasing fluorescence is related to the start of core dissolving. At this stage of the process the structure of the polyelectrolyte multilayer may change because of the nascent osmotic pressure coming from dissolved fluorescein molecules. Shortly after the beginning of core dissolution the concentration of fluorescein inside the capsules becomes constant and almost saturated, since a steady state situation between progressing core dissolution and permeation is established. One may further assume a constant concentration gradient between the shell interior and the bulk because the bulk solution can be assumed as being infinitely diluted. Therefore the rate of fluorescein penetration through the polyelectrolyte layers to the bulk becomes constant. Indeed, a linear increase of the fluorescence is observed (2). This state corresponds to the stage of dissolution depicted, in Figure 1E. The slope of the linear region decreases with the number of polyelectrolyte layers. Obviously an increasing number of adsorbed layers reduces the fluorescein penetration. After the core is,completely dissolved, ! the fluorescein concentration inside the shell equilibrates with the bulk. The driving force for diffusion decreases and the release levels off (3).
Figure 4 shows the behaviour of the permeability times thickness as a function of the numbers of layers.
Example 2: Permeability as function of pH
Sodium polyfstyrene sulfonate) (Na-PSS, MW ~ 70 000), polyfallylamine hydrochloride) (PAH, MW ~ 50 000), dextran (MW ~ 75 000 and 4 000 000), and bovine serum albumin all labeled with fluorescein isothiocyanate (FITC) were obtained from Aldrich. Hollow polyelectrolyte capsules were fabricated at pH = 7 by alternating adsorption of 8 layers PSS/PAH onto MF-particles of a diameter of 5.2 pm ( microparticles GmbH, Berlin), using
WO 02/17888 the filtration protocol (15). The cores were dissolved at pH = 1. Washings in 50 mM NaCI followed. Confocal images were taken by means of a confocal laser scanning microscope (TCS Leica). The excitation wavelength was 488 nm. The capsules were suspended into the FITC labeled polymer solution of a concentration of 1 mg/ml.
The exclusion properties of hollow polyelectrolyte capsules composed of 8 PSS/PAH layers templated on 5.2 /jm melamin formaldehyde (MF) particles for FITC-labeled dextran (with MW about 75 000) have been 10 studied as a function of pH. Fig.5 (left) provides a confocal image of capsules in the presence of FITC-dextran at pH = 10. The interior of the capsules remains dark, while the background is fluorescent. This proves that at this condition the capsule wall is not permeable for FITC-dextran. Even deformed capsules do not reveal any fluorescence inside. However, 15 at pH = 3 the capsule interior becomes as fluorescent as the bulk (Fig.5, center). This can only be explained by opening of the capsules for FITCdextran at this low pH value.
It has to be mentioned that the open and closed states at relatively low 20 pH and high pH, respectively, were observed for more than 90% of the capsules. The open state for FITC-dextran was observed for pH values up to 6. From pH 8 onwards most of the capsules are closed. At a pH value in between, i.e. pH = 7, open and closed capsules were simultaneously present.
The possibility of loading is demonstrated in Fig.5 (right) where the capsules were initially exposed to a FITC-dextran solution at pH = 3. Then the pH was shifted to 10 and the rest of FITC-dextran was removed from the bulk by centrifugation. It is remarkable that the capsules remain filled 30 with fluorescent material as shown by the fluorescence profile through the confocal image. The interior of the capsule observes a bright and constant over time fluorescence while there is no fluorescence signal from solution.
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Similar experiments of changing the capsule wall permeability by pH changes and subsequent capsule loading were performed with FITCdextran of a MW of 2 000 000 and FITC-labeled bovine serum albumin. The results are analogous to those with FITC-dextran of MW 75 000, but the pH value of the transition between the closed and open state differs by 11.5־ pH units.
Example 3: Controlling capsule wall permeability by the salt concentration
Two different types of polyelectrolyte capsules were used for these permeability experiments. 8 layers of sodium polystyrenesulfonate PSS and polyallylamine PAH were adsorbed on monodisperse templates of diameter 4.7 μηη consisting of weakly polymerized melamine-formaldehyde resin. In one batch, core dissolution was conducted at pH 1 and the subsequent washings were performed in the presence of 0.05 M NaCI. This protocol yielded crumpled capsules (Fig. 6a). These capsules were covered by two additional layers and subsequently washed with Millipore water (σ_< 18 ΜΩ cm). After this treatment, the capsules assume^ a spherical shape.
The cores in the second batch were dissolved in 0.1 M HCI and washed afterwards with Millipore water thus avoiding the addition of salt. The latter protocol yielded homogeneous population of capsules with a spherical shape (Fig. 6b). The permeability behavior of the two types of capsules was similar. Essentially the results obtained with the second type of capsules will be reported in this example. Only in case of remarkable differences results obtained with capsules having additional two layers will be mentioned.
The permeability of the capsule walls was investigated by means of fluorescence labeled polymers polystyrenesulfonate PSS (120 000 g/mol), polyallylamine PAH (70 000 g/mol), dextrane (55 000 g/mol) and human albumine (70 000 g/mol). Polyallylamine PAH was used which was labeled
WO 02/17888 at every 245<sup>th</sup> position with rhodamine B. In the Forster resonance energy transfer measurements, polyallylamine PAH labeled at every 120<sup>th</sup> position with fluoresceine was used. The capsules were added to a 5 x IO<sup>3</sup>־ M solution of the respective probe polymers, which concentration is always expressed in monomer units. The polymer permeation was followed by means of confocal imaging (TCSCN Leica, Germany). The amount of fluorescent molecules inside and outside the capsules was quantified.
The image in Fig.6b shows a confocal scan through the equatorial plane of the capsules, which were incubated with the labeled polymer solution for 24 hours. About 90% of the capsules excluded the polymers. The few with polymer filled capsules were broken and observed large holes through which the polymers could have diffused almost instantaneously into the capsule interior.
I
A similar experiment was then performed in the presence of 0.1 M NaCl. The confocal image (Fig. 6c) shows, that the interior of all capsules contains approximately the same concentration of tjie polymer as present in the bulk. This finding is consistent with an increase of the permeability of the polyelectrolyte wall for polymers in the presence of salt. This wall opening was observed for positively and negatively charged polymers as well as for the dextrane representing a neutral polymer. Hence, salt induced changes in the structure of the probe polyelectrolytes, such as coiling of the charged species cannot be the responsible mechanism for the penetration. Rather salt-induced changes of the structure and properties of the polyelectrolyte complexes in the wall have to be considered as the cause for the strong increase in permeability. As evident from the images, the fluorescent probe molecules were accumulated on the surface or inside the capsule wall. This was expected for PSS, which is adsorbed onto the positively charged capsule surface, but either for the labeled PAH an exchange of PAH molecules in the capsule wall or an adsorption to the inner PSS layer has to be assumed.
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The permeability was next investigated in dependence on the salt concentration. The capsules were mixed with 5 x 10<sup>3</sup>־ M PAH-Rhodamine and increasing concentrations of sodium chloride. The dispersions were incubated for 10 min and the amount of polymer in the interior was 5 compared with the polymer concentration in the bulk. Up to 5 x 10<sup>3</sup>־ M NaCI, no polymer penetration into the capsules was detected, but for higher concentrations, the capsules became increasingly permeable for PAH-Rh. At 2 x 10<sup>2</sup>־ M NaCI, the time of PAH־Rh penetration was estimated by means of confocal imaging overtime. The time between salt 10 addition and complete equilibration of the polymer concentration inside and outside the capsules was app. 6 min for capsules consisting of 8 layers. A slower penetration occurring within 20 min was measured for capsules of 10 layers. Confocal imaging could not follow the kinetics at higher concentrations, because the diffusion and equilibration of the polymer (' I 15 concentration was too fast. i I
The minimum amount of salt for inducing the polymer penetration was determined by incubating the capsules in polymer solution, at various NaCI concentrations for 24 hours. Then, the percentage of filled capsules was 20 determined by counting in the confocal images the number of filled and empty capsules for app. 100 capsules each (Table 1). While in the 10<sup>2</sup>־ M salt solution all capsules contained labeled polymer, in the 0.5 x 10<sup>2</sup>־ M salt solution only 16% of the capsules appeared to be filled within 24 h. In still lower NaCI, the capsules remained impermeable for the polymer. Hence, 25 the permeability increase of the capsules for macromolecules occurred within a rather narrow range of salt concentration between 0.5 and 2 x 10<sup>2</sup>־ M.
It was further examined, whether the rate limiting step of permeation after 30 the addition of salt is provided by salt-induced structure changes in the capsule wall making the wall more permeable or by the diffusion of the polymer through the layer. For this the permeation of PAH M<sub>n</sub> = 70 000
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־ was observed either immediately after the simultaneous addition of 10'<sup>2</sup> M salt (NaCl) and 5 x 10<sup>3</sup>־ M PAH or the sample was incubated for 12 hours in 10<sup>2</sup>־ M NaCl and the PAH was added only then. In the second case, it was found that the characteristic permeation time was about 30 min, 6 which was smaller than the characteristic permeation time of about 50 min observed when NaCl and the polymer were added at the same time. These numbers are two fold remarkable. They demonstrate that 1) the permeation of the polymer under the observed conditions is overall slow requiring at least 30 min for concentration equilibration, and 2) that the permeability 10 induction by salt itself requires several minutes.
Regarding the mechanism of the polymer permeation through the capsule wall two extreme situations may be distinguished. Either incubation in the salt solution led to the formation of water-filled pores through the wall 15 across which the polymers can diffuse into and out of the capsule, or the presence of ions in the solution weakens the electrostatic binding between PSS and PAH allowing for diffusion of the polymer through the network via transient bond breaking and re-establishing. Pore formation either induced by pH or by salt was observed for macroscopic flat films composed of 20 weak polyelectrolytes. These relatively large pores had a radius in the order of 10<sup>2</sup> nm. SFM was thus applied to pol'yelectrolyte capsules either prepared by drying a capsule dispersion in H<sub>2</sub>O or in 0.1 M NaCl applied onto a mica substrate. However, except the presence of some salt crystals no differences in the capsule wall topology were observed. This result 25 argued the formation of large pores as the cause of the permeability increase.
Assuming that the polymer penetration occurs via diffusion trough waterfilled pores the apparent pore cross section is of the order of 1000 nm<sup>2</sup>. 30 This would compare to either one pore of 17 nm radius or to 80 pores of 2 nm each. In any case, it is worth to note that the pore area would constitute a very tiny area fraction of the capsule surface only. From these
WO 02/17888 considerations, it becomes clear that with SFM it is hardly possible to detect these pores even if their existence is sure.
In order to find changes in the capsule wall morphology in dependence on 5 the salt concentration of the bulk electrolyte, Forster resonance energy transfer FRET between fluorescent labeled polyelectrolytes was applied. The capsules were covered by addition of six polyelectrolyte layers in the order PSS, PAH-fluoresceine, PSS, PAH-rhodamine, PSS, PAH. The polymers were adsorbed in presence of 0.5 M NaCI, but afterwards the 10 capsules were extensively washed by water. FRET of the capsule dispersion was measured 5 min after adding NaCI solutions of different concentrations. Excitation was set at 495 nm, where only fluoresceine absorbs light. If rhodamine molecules are located near the fluoresceine, (up to 6 nm) resonance energy transfer takes place and one can observe the 15 rhodamine fluorescence, too (Fig. 7, inset). ׳' ί / /
The relative transfer efficiency E<sub>fret</sub> was defined as E<sub>fret</sub> = (l<sub>rh</sub>.4l<sub>f</sub>!)/ (0.6l<sub>f)</sub> + l<sub>rh</sub>) where l<sub>fl</sub> is the fluorescence intensity at 522 nm corresponding to the maximum in fluoresceine emission and l<sub>rh</sub> is the intensity at 582 nm, 20 corresponding to the rhodamine emission.
i_
The factor 0.4 takes into account the fluorescence of the donor at the acceptor emission wavelength. The plot of E<sub>fret</sub> against salt concentration shows a clear decrease in the transfer efficiency (Fig. 7), occurring exactly 25 in the concentration range where the capsule wall becomes permeable for PAH. At higher salt concentrations, the E<sub>FRET</sub>kept almost constant. Hence, it can be concluded that FRET reported remarkable changes in the topology of the polyelectrolyte wall occurring within a narrow salt concentration range around 10'<sup>2</sup> mol/L. The decrease of E<sub>fret</sub> with the salt concentration 30 indicates an increase of the distance between the dye molecules of rhodamine and fluoresceine. The FRET signal was completely restored within 5 min when the capsules were expose to water again. These
WO 02/17888 findings are obviously consistent with some reversible swelling of the polyelectrolyte layer.
The correlation between the permeability increase of the wall opening and s FRET decrease allowed for characterizing the salt-induced capsule wall changes in the absence of a permeating polymer. The latter may have had some influence on the wall properties, especially as much remarkable amounts of the permeating polymer adsorbed to the wall. The capsules were introduced in 1.5 x 10'<sup>2</sup> M NaCi and the E<sub>fret</sub> was measured in 10 dependence on the time (Fig. 8). After 20 min the FRET was saturated at a value of E<sub>fret</sub> = 0.31. The time scale of the changes was consistent with the permeability change observed by means of confocal microscopy. Both, the time and the degree of the FRET signal change related to wall structure changes increased with the salt concentration.
/ 15 i i
The mechanism and driving forces causing both layer permeability increase and the decrease of the fluorescence energy transfer occurring in a narrow salt concentration range are discussed below. The rpther slow permeation indicates, if water-filled pores are assumed as the basic pathway for 20 permeation, a very small pore area. On the other hand, the charge of the FRET signal can only be understood assuming conformational changes affecting the majority of the labeled polymers. Hence, salt induces layer changes throughout. This is less constant with assuming the much\ ו localized formation of a׳ small number of pores. Therefore we interpret the 25 permeability increase as a result of an increased solubility or interactions of the permeability species with the layer polymers, which are caused by an increased salt concentration.
A higher salt concentration was found to soften the structure of the layer 30 because the ion pairs found between the polyanions and the polycations may partly open, because the free ions available in the bulk would screen the charges in the layer. Layer swelling can thus be understood as a
WO 02/17888 < molecular elasticity relaxation of the polymer pairs, leading to a more bulky J arrangement of the layer polymers. It is worth to note that at 10<sup>2</sup>־ M NaCI the Debye screening length is just 3 nm comparing well to a layer thickness increment of a polyanion/polycation pair. At lower electrolyte 5 concentrations, the electrostatic interactions have a larger range providing an electrostatic interaction over the whole layer.
An important issue for many applications is the reversibility of the permeability switching process. The fact, that the capsules were prepared at high salt concentrations and are nevertheless impermeable for the I macromolecules after washing demonstrates the reversibility of the capsule opening and closing. In further experiments the time of closing the capsule wall was determined. A 3 x 10'<sup>2</sup> M NaCI solution was applied for 30 min to the capsules. Afterwards they were diluted into pure water to app. 5 x 10<sup>3</sup>־<sup></sup>I
M NaCI. After ten minutes, the capsules became impermeable for the PA.HRhodamine as was observed by means of confocal imaging. The FRET signal was recovered within 5 min (Fig. 8).
The reversibility of the wall permeability change for polyelectrolytes allows <
for an easy and soft encapsulation of macromolecules, such as ί polypeptides, DNA, enzymes, or polymers avoiding any chemical stress caused by aggressive substances, solvents, pH, or heat applied during encapsulation. However, loading of capsules with macromolecules at high salt concentration following by washing with water yielded only small amounts of encapsulated polymer in the interior. Probably, the macromolecules were washed out faster than the wall closed.
A much higher efficiency of loading was however achieved when the j polymer for encapsulation was present in the bulk during closure of the j
I 30 wall induced by salt removal. (Fig. 10). By this way, the capsules were loaded with a 5 x 10'<sup>3</sup> M PAH-Rh solution (Fig. 9). Taking the fluorescence intensity of the confocal image of the PAH-Rh solution as standard, the
WO 02/17888 amount of encapsulated polymer could be determined. The average of the interior PAH-rho concentration was about 50% of that of the initial solution.
Another important property of the loaded capsules is their release behavior. The loaded capsules were incubated for 30 min either in 2 ml water or in 2 ml of a 3 x 10'<sup>z</sup> M salt solution. The capsules were removed from the sample by centrifugation and the concentration of the PAH-Rh in both solutions was determined by fluorescence spectroscopy.
The dependence of the rhodamine emission on the salt concentration, was taken into account by means of adjusting the salt free solution afterwards to 3 x 10<sup>2</sup>־M before the measurement were performed.
: i While in the pure water the amount of released PAH could not be detected almost all encapsulated PAH-Rh was released in 3 x 10‘<sup>2</sup>M NaCI. Confocal image proved that the interior of those capsules was void of fluorescent polymer again.
i
Example 4: Temperature dependent permeability
Monodisperse spheres (d = 5.94pm) of a weakly polymerized melamineformaldehyde resin were used as templates (Microparticle GmbH). The particles were covered׳ by alternating adsorption of sodium polystyrene sulfonate PSS (MW 70 000 g mol'<sup>1</sup>, Aldrich) and polyallylamine hydrochloride PAH (MW 70 000 g mol'<sup>1</sup>, Aldrich) from an aqueous solution of 10<sup>2</sup>־ M PSS in 0.1 M sodium chloride. After 8 layers the core was dissolved in 0.1 M hydrochloric acid. The decomposition products were removed by washing with acid and an aqueous solution of 10‘<sup>2</sup> M NaCI. Hollow polyelectrolyte capsules remained. In order to remove some defects in the capsules wall caused by mechanical stress during the dissolution two additional layers were coated on the capsules after the dissolution of
WO 02/17888 the cores. Afterwards the capsules were washed extensively (8 times) with
Milli-Q־water (resistance >18 ΜΩ cm’<sup>1</sup>). By this procedure, traces from salt and protons were essentially removed and a pH value of 6 was reached.
For the study of the permeability, fluorescence labeled polymers were used. PAH (MW 70 000, 1 rhodamine molecule per 245 PAH units and MW 15 000, 1 rhodamine per 320 PAH units) and PEI (MW 2 000, 1 fluoresceine molecule per 650 PEI units) were labeled by reaction with rhodamine isothiocyanate or fluoresceine isothiocyanate. Labeled PSS (1 rhodamine molecule per 600 polymer units) was synthesized by copolymerization of styrene sulfonate with methacroyloxyethyl thiocarbamoyl rhodamine B (Polyscience). The MW of the polymer was determined being 120 000 g/mol by gel permeation chromatography. Fluoresceine labeled human serum albumine (MW 69 000) and rhodamine labeled dextrane (MW 40 000 g/mol) were purchased from Aldrich company.
Laser scanning microscopy was performed for the determination of the loading grade of the capsules. An inverse research microscope (Leica, Germany) with either a 40 x or a 100 x oil immersions objective was used. The amounts of polymer/monomer in the interior were determined by integration of the fluorescence intensity inside the capsules. The exact concentration was taken from calibration curves, determined for each fluorescent probe separately. Due to the broad distribution of permeability for the capsules, statistical values were taken from 5 capsules each. Capsules, which could be recognized clearly as broken once (appr. 20%), were excludes from the determination. The temperature dependent measurements were done with an home-made aluminium device on top of the sample, by which the temperature was settled by an electronic controller.
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Scanning force microscopy was applied to capsules, dried on air on a mica substrate. The drying process after the heat treatment at 60°C was done by transferring a drop of the capsule solution to the mica surface and drying without any change of the temperature.
4.1 Permeability
The permeability of the capsules was studied for positively (PAH) and negatively charged (PSS), zwitterionic (albumine) and noncharged (dextran) fluorescent polymers (dextran). In general, the capsules were mixed with סו the probe polymers in a concentration of about 2 x 10'<sup>3</sup> mol/L with respect to the polymer units and incubated for 15 min. Then, the fluorescence intensity in the center of the capsules was measured by confocal imaging. The fluorescence events within the cross section of the capsule were integrated and compared with the fluorescence events in the bulk solution. 15 Less fluorescence intensity inside than outside the capsules indicates an impermeability of the capsule wall for the probe polymer. Equal fluoroscence intensities inside and outside of the capsules at the start of the experiment is caused by fast penetration of the ,polymers through the capsule wall, mostly observed for broken capsules. In case of dextrane as 20 described below the fluorescence inside the capsules is higher than in the bulk phase indicating an accumulation of the' polymer in the interior.
First the permeability of the capsule wall for the probe polymers was studied before any heat treatment. Within 24 hours the majority of 25 capsules were impermeable for charged polyelectrolytes of MW above 60 000 g/mol independent on the sign of the charge. Figure 11a shows the confocal image for PAH of 70 000 g/mol. In the case of uncharged dextrane an unusual accumulation of the polymer inside of appr. 20% of the capsules was observed (Fig. 11 b), while the other capsules exclude the 30 polymer, too.
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Further influence of the length of the polymer chain on penetration was determined. While within 1 hour 80% of the capsules are impermeable for PAH 70 000 g/mol, about 65% were impermeable for PAH 15 000 g/mol and for PEI 2000 all capsules were permeable. Small dye molecules such 5 as fluoresceine, rhodamine and acridine orange can penetrate the capsule wall independent of their charge.
The dependence of the permeability of capsule walls on temperature was followed online by confocal imaging (in situ) by heating capsules in 10° 10 steps from room temperature to 80°C. At each step the temperature was allowed to stabilize for 5 min. The changes in the polymer distribution within the capsules and the bulk solution were similar for each polymer and are demonstrated for heating the capsules in presence of rhodamine labeled PSS. Up to 50°C the polymers was excluded from the capsule 15 wall, but at higher temperature the PSS starts to flow into the capsules until an equilibrium or even a slight excess was reached inside the capsules. The rate of penetration increases with the temperature furthermore. This is a clear proof, that the capsule vyall can be opened for large polymer molecules very easy by increase of the temperature.
It was further examined whether the opening is an irreversible process or if the capsule walls can be closed again by reducing the temperature below 50°C. This was investigated by treating the capsules in absence of polymers at different temperature conditions deviating in time of heating 25 and cooling.
Possible mechanisms leading to an increase of capsule wall permeability are discussed below. Besides the fact, that diffusion through a membrane increases generally with temperature due to the higher mobility of the 30 polymer species, the rather strong effect observed in a narrow temperature range indicates structural changes in the polyelectrolyte wall. One possible mechanism could be the opening of pores in the polyelectrolyte membrane
WO 02/17888 as it is described above for treatment with pH and salt for similar systems. It was observed that PSS/PAH capsules shrink at higher temperature by more than 10% in diameter. The mechanical stress at such process could cause also the formation of pores. In order to find such pores, the capsule wall was investigated by high resolution Scanning Force Microscopy after drying capsules on a mica substrate. Three samples were prepared before, during, and after heating to 60°C, but significant differences were not observed apart from the reduction of the capsules in diameter. Despite of this experimental result, the formation of pores can not be fully excluded because of the subsequent drying process can change the capsule structure remarkably.
Another mechanism is the weakening of the electrostatic bounds between polyanions and polycations. This leads to an increased charge density in the film, connected with stronger hydration, swelling and a better diffusion of the polymers through the wall. It was tried to support this mechanism by investigations of the resonance energy transfer in capsules consisting of 14 layers, in which the 10th layer is PAH-fluoresceipe and the 12th layer is PAH-rhodamine. The spectra of the solution were taken before, during, and after heating to 60°C for 20 min. The spectra before and after the heating look quite similar, indicating an almost reversible change in the wall structure. The spectrum at 60°C deviates remarkably from the other sp.ectra. The decrease of the rhodamine fluorescence indicates an increase of the averaged distance between fluoresceine and rhodamine molecules or the polymer layers, respectively. In order to exclude simple heating effects as origin of the observed spectra changes, a PAH polymer containing on every 106th position a fluoresceine molecule and on every 345th position a rhodamine molecule (MW 70 000 g/mol) was investigated under identical conditions.
The findings offer a unique possibility to encapsulate macromolecules, since the permeability of capsule walls was found to be controlled by
WO 02/17888 temperature: the capsule wall is opened by heating and surrounding material can stream in. If the capsules are filled with the desired materials the wall can be closed again by cooling down the solution. Afterwards the remaining materials outside, e.g. polymers can be washed away and the 5 enclosed macromolecules remain inside the capsules. The encapsulation was done successfully for all labeled polymers by heating impermeable capsules (Fig. 12a) to 60°C for 20 min. After cooling and washing, the capsules contained the polymer as shown for example in Figure 12b. A quantitative determination of the fluorescence intensity of the original 10 polymer solution and the encapsulated polymer in the interior yielded a 30% of the bulk concentration in the interior. Both probe polymers used,
i.e. labeled PSS as well as PAH were captured in the interior indicating a high reversibility of the permeability. Even storage of the filled capsules for more than one month lead only to some loss of polymer. This loss was 15 especially strong with׳ more than 50% for PAH, but zero in case.of dextrane.
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References
1. G. Decher, Science 1997, 277, 1232
2. B. Miksa, S. Stomkowski, Cooloid Polym. Sci. 1995, 273, 47
3. G. Crofts, T.G. Park, J. Control. Release 1995, 35, 91
4. K.B. Thurmond, T. Kowalewski, K.L. Wooley. J. Am. Chem. Soc. 1997, 1997, 119, 6656.
5. G.B. Sukhorukov, E. Donath, H. Lichtenfeld, E. Knippel, A. Budde and H. Mohwald, Colloids Surfaces A, 1998, 137, 253
6. E. Donath, G.B. Sukhorukov, F. Caruso, S. A. Davis and H. Mohwald, Angew. Chem. lot. Ed. 1998, 37, 2202
7. G.B. Sukhorukov, E. Donath, S.A. Davis, Heinz Lichtenfeld, F. Caruso, V.l. Popov and H. Mohwald, Polym. Adv. Technol., 1998, 9, 759
8. G.B. Sukhorukov, M. Brumen, E. Donath and H. Mohwald, J. Phys. Chem. B 1999, 103, 6434
9. G.B. Sukhorukov, E. Donath, S. Moya, A.S. Susha, A. Voigt, J. Hartman and H. Mohwald, J. Microencapsulation, 2000, 17, 2, 177-185
10. S. Moya, et al. Macromolecules, 2000
11. R. von Klitzig, H. Mohwald, Macromolecules 1S|96, 21, 6901
12. S. Leporatti et al. Langmuir, 2000
13. a) E. Donath, G. B. Sukhorukov, F. Caruso, S. Davis, H. Mohwald. Angew. Chem. 1998, 7 70, 2323; Angew. Chemie, Inter. Ed. Eng., 1998, 37, 2201;
14. F. Caruso, R. Caruso, H. Mohwald, Science, 1998, 282, 1111.
15. A. Voigt H. Lichtenfeld, G. B. Sukhorukov, H. Zastrow, E. Donath, H. Baumler, H. Mohwald, Ind.&Eng.Chem.Res, 1999, 38, 4037.
16. G. Decher, J.-D. Hong, Makromol. Chem., Macromol. Symp. 1991,46, 3211.
17. E. Donath, G. B. Sukhorukov, H. Mohwald, Nach. Chem. Tech. Lab., 1999, 47, 400.
18. I. L. Radtchenko G. B. Sukhorukov, S. Leporatti, G. B. Khomutov, E. Donath, H. Mohwald, J.Col.&lnt. Sci, (2000), in press.
19. L. Dahne et al., Angew. Chem. (2000).
WO 02/17888
20. A.Kabanov, A.Zezin, Pure Appl. Chem., 1984, 56, 343.
21. B. Philipp, H. Dautzenberg, K.-J-Linow, J. Kotz, W. Dawydoff, Prog. Po/ym. Sci., 1989, 14, 91.
22. J. D. Mendelsohn, C.J.Barret, V.V.Chan, A.J.Pal, A.M.Mayes, 5 M.F.Rubner, Langmuir (2000), in press.
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Table 1: Percentage of filled capsules after 24 hours incubation time in solutions of PAH-rho, 5x1 O'<sup>3</sup> M and in presence of different salt concentrations.
<td> Salt concentration /10<sup>4</sup> mol/L</td><td> 1</td><td> 5</td><td> 10</td><td> 50</td><td> 100</td><td> 200</td>
<td> Percentage of filled capsules/ %</td><td> 4.6</td><td> 8.5</td><td> 6</td><td> 16.7</td><td> 100</td><td> 100</td>
Μ © Copyright 2003 by Humana Press Inc.
All rights of any nature whatsoever reserved.
1085-9195/03/39/23-43/$20.00 i
'Review Article
Biomedical Applications of Electrostatic Layer-by-Layer Nano-Assembly of Polymers, Enzymes, and Nanoparticles
Hua Ai,*<sup>1</sup> Steven A. Jones, and Yuri M. Lvov*
Department of Biomedical Engineering and Institute for Micromanufacturing, Louisiana Tech University, Ruston, LA 71272
Abstract
The introduction of electrostatic layer-by-layer (LbL) self-assembly has shown broad biomedical applications in thin film coating, micropatteming, nanobioreactors, artificial cells, and drug delivery systems. Multiple assembly polyelectrolytes and proteins are based on electrostatic interaction between oppositely charged layers. The film architecture is precisely designed and can be controlled to 1-nm precision with a range from 5 to 1000 nm. Thin films can be deposited on any surface including many widely used biomaterials. Microencapsulation of micro/nanotemplates with multilayers enabled cell surface modification, controlled drug release, fallow shell formation, and nanobioreactors. Both in vitro and in vivo studies indicate potential applications in biology, pharmaceutics, medicine, and other biomedical areas.
Index Entries: Layer-by-layer; self-assembly; silicone rubber; thin films; shell; micropatteming; microencapsulation. .
INTRODUCTION
Electrostatic layer-by-layer (LbL) self-assembly (1-4) has been applied to thin film coating (5-8), micropatteming (9-11), nanobioreactors (12,13), artificial cells (14), drug delivery systerns (15,16), and even electronic devices (17-19). The LbL technique is based on alternate adsorption of oppositely charged materials, including linear polycations and polyanions.
* Authors to whom correspondence and reprint requests should be addressed. E-mail: ylvov@coes.latech.edu; hxa47@po.cwru.edu. <sup>1</sup>Present address: Department of Biomedical Engineering, Case Western Reserve University, Cleveland, OH 44106.
Multilayers of materials can be assembled on two-dimensional (2-D) supports of any area (slides, silicon wafers, plastic surfaces) and on three-dimensional (3-D) micro/nanotemplates (colloidal particles, such as latex or cells). Charged materials, including linear polyelectrolytes (synthetic and natural), enzymes, antibodies, viruses and inorganic nanoparticles have been used in 2-D and 3-D nanoassembly processes (1-24). The architecture of the resulting film can be designed with nanometer preci־ sion (in cross-section) to meet different requirements such as thickness, biocompatibility, controlled permeability, targeting, and optical or magnetic properties.
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<img file="IL190885A_D0050.tif" />
Fig. 1. The procedure of electrostatic layer-by-layer self-assembly on. 2-D substrates and 3-D micro/nanotemplates.
LbL technology has been widely studied in the past few years (1-3). Successful achievements are noteworthy, but practical clinical applications remain to be developed. This review focuses on the major characteristics of this technique and current applications in biomedical fields.
The assembly procedure is briefly shown in Fig. 1. The 2־D and 3-D applications are shown in parallel because the same working principle is used. A solid support (e.g., slide) or collection of micro- or nanotemplates (e.g.<sub>׳</sub> latex cores or cells) with negative surface charge is incubated in the solution containing the cationic polyelectrolytes, and a layer of polycation is adsorbed (step 1). Because the adsorption is carried out at a relatively high concentration of polyelectrolytes, a number of ionic groups remain exposed at the interface with the solution, and thus the surface charge is effectively reversed. The reversed surface charge prevents further polyion adsorption. Solid supports or microtemplates are then rinsed with pure water or washed by centrifugation, respectively to remove excess free polyions. The surface is then immersed in a solution of anionic polyelectrolytes (step 2). Again, a layer is adsorbed, but now the original surface charge (negative) is restored and the surface is ready for further assembly (step 3). These two steps are repeated alternately until a layer of the desired thickness is obtained. More than two components can be used in the assembly with one condition: a proper altemation of positive and negative compounds.
The main idea of tire method consists of resaturation of polyion adsorption, resulting in the alternation of the terminal charge after every subsequent layer deposition. This idea is general and implies that there is no principle restriction to the choice of polyelectrolytes. Ultrathin ordered films could be designed with molecular architecture plans (3) in the range of 5-1000 nm, with a precision better than 1 nm and a definite knowledge of their molecular composition.
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Layer-by-Layer Nano-Assembly
WHY LAYER-BY-LAYER THIN FILM COATING?
The ability to construct thin films on a variety of surfaces has multiple biomedical applications. Coatings on medical devices can improve biocompatibility reduce the immunological response, and deliver a drug locally. It is thus useful to find a method to coat thin films with required properties on a variety of surfaces. For example, a thin (only few nanometer) film coating on Petri dish can promote cell adhesion and growth in vitro. Currently available thin film methods include spin coating and solution casting, thermal deposition, polyion layer-by-layer assembly, chemical selfassembly, the Langmuir-Blodgett technique, and free-standing films. The optimal combination of molecular order and stability of films determines the practical usefulness of these technologies (1-3,25). A primary advantage of the LbL self-assembly technique is its ability to coat thin films with ordered structure and nanometer thickness on supports of various shapes and sizes.
THIN FILM PROPERTIES
Ionic strength, pH, and concentration of the polyion solution affect LbL assembly, film thickness and stability. For the LbL process, the pH of the polyelectrolyte solutions should be selected to maintain a high degree of polyion ionization. The negative charge of the polyanions is often achieved by pendant sulfonate groups with pKa = 1 or carbonate groups with pKa around 4-5. Cationic properties of polymers are often controlled by ionization of amino- and imino- groups that have isoelectric points around pH 8 and 11, respectively. Therefore, phosphate-buffered saline (PBS) at pH 7.4 is appropriate to maintain the charge of many polyanions and polycations, including polysaccharides. PBS also provides physiological ionic strength, which is important for protein or enzyme assembly. If the pH value of the coating solution is too
Cell Biochemistry and Biophysics close to the isoelectric point (PI) of the polyions used, the charge is not sufficient to. support LbL assembly (at least 10% of pendant groups have to be ionized). The thickness of each layer in the LbL film can be finely adjusted by changing the ionic strength of the solution, which in turn induces polymer coil formation. Higher ionic strength leads to a thicker film. Alternating adsorption of poly(styrenesulfonate)/poly(dimethyldiallyl ammonium chloride) from solutions with ionic strength 0.01 M NaCl and 1 M NaCl resulted in the bilayer growth step variation from 1.6 nm up to 6 nm (3). Typically, in LbL assembly linear polyion solutions with concentration of O.h-3 mg/mL were used, and a deposition time for monolayer formation was 10-15 min.
Quartz crystal microbalance (QCM) monitaring of multilayer growth is efficient in estimation of film thickness assembled on different supports. The frequency shift of a QCM resonator with adsorption cycles is proportional to the adsorbed mass at every assembly step. The relationship between adsorbed mass M (g) and frequency shift ΔΡ (Hz) for a 9־ MHz quartz resonators is: AF = -1.83 x 10<sup>8 </sup>M/A, where A = 0.16 ± 0.01 cm<sup>2</sup> is the surface area of the resonator (26). A 1-Hz frequency change in ΔΡ corresponds to a 0.87-ng mass adsorption (27), and a film's thickness can be calculated from its mass. Other powerful tools, such as X-ray reflectivity, atomic force microscopy, and scanning electron microscopy, have been used in monitoring film thickness and surface morphology. It was found that for linear polyion LbL films a typical bilayer growth step is 1.5-2 nm, a film surface roughness is of approx 1 nm, and total films may be prepared in the range 5-1000 nm depending on the number of adsorption cycles (1-4).
Polyion films are insoluble in water and in many organic solvents and are stable up to at least 250°C (28). Hydrophilic films formed by LbL self-assembly remained stable after 1-mo incubation in a 90°C oven, whereas a plasmatreated polymer surface lost its hydrophilic surface property after a few days (29).
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Ai, Jones, and Lvov
THIN FILMS ON SOLID SUPPORTS
Medical Implants
Most medical implants lack a biointerface between the implant and the surrounding tissue. Local nonspecific, protein adsorption, inflammation, and infection can interfere with long-term use. The rationale for the surface modification of biomaterials is straightforward: retain the key physical properties while modifying only the outermost surface to influence biointeraction (30). Usually a hydrophilic coating with lubricious property on implants is favorable for prolonging the lifetime of the product. Nonspecific adsorption of proteins should be minimized and beneficial molecules should become. selectively adsorbed onto biomaterials as a result of modifications performed before their implantation (31). The LbL self-assembly technique can be used to deposit thin films on implants for such functions.
Ideally, alternation of only the outermost molecular layer (3-10 Angstrom) should be sufficient but thicker films are necessary to ensure a full coverage on the original surface of a medical implant (30). The LbL self-assembly technique enables us to coat ultrathin ordered films in nanometer range and with definite knowledge of their molecular composition (3). Anonlinear film growth often occurs at the beginning of the alternating assembly process (32,33). The first two to three layers have smaller amounts of adsorbed polyion. The film mass and thickness of subsequent layers increase linearly with the number of adsorption cycles. The desired film thickness will depend on the coating material, the implant surface roughness, and tine biological environment of the implant. Films of sufficient thickness can alter mechanical properties and surface morphology, whereas films that are too thin will not provide the desired durability and strength.
Natural polymers are of interest in polymer film assembly because of their unique characteristics. They are naturally available, nontoxic, and biocompatible. Proteins and protein-based polymers (albumin, collagen, and gelatin), polypeptides (polylysine, poly(a,L-glutamic acid), poly(aspartic add)), and polysaccharides (hyaluronic acid, dextran, heparin, chondroitin, and chitosan) can be used in LbL assembly.
Synthetic polymers have also been used in the assembly procedure. Commonly used polyions include polycations, such as poly(ethyleneimine) (PEI), poly(dimethyldiallyl ammonium chloride) (PDDA) and poly(allylamine) (PAH), and polyanions such as polystyrenesulfonate) (PSS), poly(vinylsulfate), and poly(acrylic add) (PAA) (Fig. 2). For the suecessful assembly of protein multilayers, it is important to use linear or branched polyion interlayers. Flexible linear polyions penetrate between protein globules and act as electrostatic glue. The concept of electrostatic polyion glue, which keeps together neighboring arrays of proteins, is central to protein and nanopartide assembly.
Cell-resistarit polymeric materials such as. polyethylene glycol (PEG) (34) have been developed as coatings to reduce adsorption of serum and cell-bome proteins. The application of PEG was limited by low peptide grafting, which reduces protein adhesion (34). Dextran, a mucilaginous polymer of glucose, has more peptide grafting sites than PEG, which tends to־ reduce protein adsorption on biomaterials (35). The current limitation in using dextran as a cell-resistant surface coating for biomaterials is that the reagents used for surface coupling are highly toxic, expensive, and require stringent anhydrous reaction conditions (35). Multilayers of chitosan/PSS (36) or chitosan/dextran sulfate (37) were assembled through LbL selfassembly. The presence of 0.5 M or higher concentration of NaCi in the coating material solution enabled the anticoagulant function of sulfonated dextran (37). At a higher NaCi concentration polymers are in a coiled shape when absorbed onto the film surface. This coiling means that excess charges, which do not participate in the polyion complex formation with cationic chitosan, are present on the outermost surface of the polymers. Because the anticoagulant activity of dextran can be attributed to the sulfate groups of the polymer, the excess
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Layer-by-Layer Nano-Assembly (—CH2-,----T-CH2—Ϊ \ /n
M cr
CH<sub>3</sub>'' <sup>+ X</sup>CH3
Pofy(dlmethyldlally ammonium chloride) (PDDA+) '— CH<sub>2</sub>CH<sub>2</sub>ijH<sub>2</sub> — <sup>4</sup> 41
Poly(ethylonlmlne) (PEJ+) (—CH—CH<sub>2</sub>--) (—CH—CH,— )
A <sup>n</sup> 1 <sub>+</sub> . <sup>n</sup> fj ch<sub>2</sub>Sh<sub>3</sub>ci
SOjNa<sup>+</sup>
Poly(styrene8ulfonate) (PSS-) Poly(allylamlne hydrochloride) (PAH+)
Fig. 2. Chemical structures of commonly used synthetic polymers.
charges on the dextran film surface prepared in the presence of suitable concentrations of NaCl seem to result in intact activity (37). Other multilayers may also reduce cell adhesion. The assembly of (poly(lysine)/alginate)5 multilayer above a gelatin (of 'extracellular matrix) surface resulted in a 200-fold decrease in the adsorption of human fibroblast cells, as compared with the untreated surface (7).
Hydrophilic materials are more resistant to bacterial adhesion than hydrophobic materials (38). Albumin adsorbed on material surfaces has shown obvious inhibitory effects on bacterial adhesion to polymer, ceramic, and metal surfaces (39). Implants with crosslinked albumin coatings had a much lower prosthetic infection rate than uncoated implants in a rabbit model (40). An albumin/heparin multilayer assembly for biocompatible coatings was developed through the LbL technique with the albumin adsorption density of 0.15 mg/cm<sup>2</sup> at physiological pH 7.4 (41). Thus, a coating can be achieved on medical implants through the LbL technique to reduce bacterial adhesion.
Hyaluronic acid (hyaluronan), a naturally occurring׳ biopolymer׳ in'the category of poly saccharides, is also widely used as a hydrophilic coating. The lubricity, hydrophilicity, and biocompatibility enable its applications not only in coatings but also in topical, injectable, and implantable vehicles for the controlled and localized delivery ofbiologically active molecules (42). We have assembled hyaluronan/polyelectrolyte multilayers on silicone rubber with increased hydrophilicity (43) . The contact angle of the hyaluronan layer was 75 + 6 degrees, when compared to 107 + 2 degrees for the original silicone rubber surface. The film thickness grew linearly with the number of layers. The averaged hyaluronan layer thickness was 1.8 ± 0.4 nm.
For biomaterials that come into contact with blood, minimization or elimination of thrombogenicity is a major concern. Multilayers of biopolymers and proteins have shown cellresistant and hydrophilic properties that can also be used for antithrombotic applications. Vascular stents coated with hyaluronic acid (44) , heparin (45), albumin (46), or dextran (dextran stent) have shown improved thromboresistance ' and lower platelet adhesion.
־ These coatings can also be achieved through
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LbL assembly. Coating materials and coating thicknesses can be - readily adjusted in the assembly procedure.
The LbL technique is currently being used in industry by Ciba-Vision/Novartis. The technique deposits LbL multilayers on plastic lenses for the eye to make them biocompatible (L. Winterton, J. Lally, M. Rubner, Y. Qiu, US Patent Appl. #20010048975, February 1, 2001). It is necessary to increase the speed of LbL assembly for a large-scale production process. In a number of companies, different combinations of polypeptides and polysaccharides adsorbed in alternation with proteins or oppositely charged synthetic polyions (for example, heparin/albumin, heparin/PEI) were used as blood anticlotting coating. Fixation of protein/ polyion architecture can be achieved by glutaraldehyde treatment of multilayers. Brynda and Houska demonstrated such fixation for an albumin /heparin multilayer by immersing the multilayer in a 5 mg/mL solution of glutaraldehyde for 30 min (41). Glutaraldehyde forms covalent bonds between amino groups of basic amino acid residues of albumin and some unsubstituted amino groups of heparin. Other cross-linking agents may be also used for this purpose.
In vivo biocompatibility testing of the LbLassembled thin films is important to explore further clinical applications. Films based on humic acids (HAs) have been coated by LbL assembly on implantable glucose sensors to increase biocompatibility and control glucose permeability (48). in vivo studies in rats indicated mild tissue reaction along with some neovascularization around the HAs/Fe<sup>3+</sup>coated implants after 4 wk of implantation. Moreover, no significant fibrosis around the implant was discovered. As with other LbLassembled biofilms, the HAs/Fe<sup>3+</sup> film growth is dependent on the pH and ionic strength in solution. The shear modulus increased linearly with the number of layers deposited and reached 80 MPa at 200 nm, which is soft and pliable and thus miriimizes tissue damage.
LbL assembly is possible on biological surfaces. It overcomes a fundamental obstacle pre venting the use of colloidal materials on biosurfaces; self-assembly onto a proteinaceous surface is hindered by the heterogeneity of the chemical groups on such surfaces, LbL polyion assembly covers heterogeneous surfaces and makes them inert in biological liquids. The assembly of a (poly(lysine) /alginate)<sub>5</sub> multilayer above the gelatin (or extracellular matrix) surface resulted in a. 200-fold drop in the adsorption of human fibroblast cells, as compared with the untreated surface (7). This method is useful because it allows treatment of a limited area of tissue via multiple rinsing steps with polyelectrolyte solutions and it can generate a thin coating on tissue surfaces that is inherently biocompatible and biodegradable. Recently, a progress for spray deposition of polycation/polyanion multilayers has been developed that is more suitable for coating tissue surfaces than alternate dipping method (8).
Surface Modification of Silicone Rubber
Thin polyion films can be deposited on silicone rubber through the LbL self-assembly without the need for other surface pretreatment such as chemical modification. Silicone is a biomaterial that is widely used in major applications such as vascular grafts, catheters, heart valves, artificial joints, and breast implants, However, its applications are limited by side effects of its high hydrophobicity. These side effects include protein and lipid deposition on contact lenses (49-50), the foreign-body reaction caused by joint implants (51), lipid infiltration in breast implants (52), and lipid absorption by silicone heart valves (53).
We coated thin polymer films on flat and textured silicone rubber surface through LbL assembly. Silicone rubber is usually modified with oxygen plasma treatment to make it hydrophilic, but the hydrophilicity is temporary (54). In our case, no pretreatment was used to make the base silicone rubber surface hydrophilic. Multilayers of PSS and PEI were directly coated as the precursor film on silicone rubber through LbL assembly (11,55). Since the silicone is hydrophobic without surface
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Layer-by-Layer Nano-Assembly charge, the mechanism of adsorption of negatively charged PSS'polyions is not well under- ׳ stood. Hydrophobic forces may account for the assembly. This suggestion is consistent with studies of LbL assembly as a method for polymer surface modification (56,57). Once the first layer is formed, the second positively charged PEI layer is adsorbed on the PSS layer by electrostatic interactions. Two or three bilayers of PSS and PEI are essential to build a foundation for further assembly of biopolymers or proteins. Polylysine, gelatin, fibronectin, laminin, or hyaluronic acid can then be added as biocompatible coatings.
The measurement of contact angle was a simpie but efficient method to monitor film growth on silicone rubber, The contact angle switched systematically from 73 to 84 degrees as the outermost layer was changed from PEI to PSS, and from 51 to 59 degrees as gelatin and PDL were alternated (11). Therefore, the outermost layer of the film dominated the surface charge and determined its hydrophilicity (29). Surface wettability was modified depending on the outermost layer. A gelatin outermost layer had the smallest contact angle of all outer materials examined and it was used to modify silicone rubber .surfaces (11),. .The film composed of gelatin multilayers was hydrophilic, as verified from contact angle measurements. Figure 3 shows contact angle for a silicone rubber surface modified by alternate adsorption of polyD-lysine (2 nm thick layer) and gelatin (3-nm layer) based on (PSS/PEI) 3־bilayer precursor film. Only 3-4 bilayers are required to change the contact angle from 107 to 51 degrees.
The coating on a QCM electrode with the architecture of [(PEI/PSS)4 + (PDL/Gelatin)12] was observed under a scanning electron microscope, The film thickness estimated from this method agrees with the QCM measurements of 70 nm. The gelatin film supported adhesion and growth of bovine coronary artery endothelial cells throughout a 2-wk experiment, whereas cells seeded on an unmodified silicone rubber surface became unviable. The assembled gelatin nanofilm on silicone rubber was stable for cell adhesion and growth throughout
<img file="IL190885A_D0051.tif" />
Adsorption Layers
Fig. 3. Contact ׳angle measurement of each adsorption layer. PSS and PEI were used to build up the precursor film of (PSS/PEI)3. Gelatin and PDL layers were further assembled.
the experiment. Figure 4 compares the cell adhesion on unmodified and gelatin coated silicone rubber after 72 h of seeding.
It can be advantageous to grow cells on a 3D support rather than a flat surface. A microtextured biomaterial solid support provides both a 3-D space, in which cells may proliferate, migrate, and differentiate, and a surface environment that directly or indirectly promotes desirable cell behavior (58). Silicone rubber with microstructures has been widely used for cell adhesion and orientation (58-59). Unmodified silicone rubber is hydrophobic, so surface modification is necessary to improve hydrophilicity for cell adhesion and spreading. We have coated a thin film containing polyion/gelatin multilayers on a silicone rubber microchannel surface. Smooth muscle cells showed a clear preference for alignment along the sidewall of the 100-pm channel surface. Cell adhesion on unmodified silicone rubber microchannels did not show a clear alignment pattern. These types of studies of cell behavior on textured surfaces with biologic interfaces are appropriate for analysis of cell-microarchitecture interactions. '
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<img file="IL190885A_D0052.tif" />
<img file="IL190885A_D0053.tif" />
Fig. 4. (A) Endothelial cells adhesion on the silicone rubber at 3 d (100 x). (B) Endothelial cells adhesion on the [(PSS/PEI)4 + (gelatin/PDL)4 + Gelatin] film after 3 d (100x).
Deoxyribonucleic Acid and Protein Thin Films
Deoxyribonucleic acid (DNA) and polynucleotides (polyuridylic and polyadenylic acids) can be readily assembled in alternation with polycations (PEI, PAH, polylysine) (60-62). Alternate adsorption of 0.1 mg/rnL DNA at pH 5.2 with pblycations gave multilayers with a DNA/PEI bilayer thickness of 4.4 nm and DNA/PAH bilayer thickness of 3.6 nm. FT-IR spectra confirmed the native doublestranded DNA conformation in DNA/PEI and DNA/PAH multilayers (62). Coating DNA/ polyion films on medical implants may have applications in local gene therapy.
Proteins including lysozyme (63), horseradish peroxidase (64), albumin (41), Bacteriorhodopsin
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Layer-by-Layer Nano-Assembly (24), immunoglobulins (14,71), glucoamylase (65), glucose oxidase (GOx) (26,64), catalase (66), glucose isomerase (67), and diaphorase (27,68) were used at a concentration of 0.1-2 mg/mL for LbL assembly. Because the surface structure of the solid support can affect the stability of proterns, precursor films of alternate PEI/PSS were used as standard surfaces. Proteins immobilized in multilayers with strong polyions, such as PSS, PEI, and PDDA were insoluble in buffer for a pH range between 3 and 10. Protein multilayers with weak polyions were partially soluble in solutions with a pH close to the isoelectric point of one of the components, but such multilayers can be stabilized with crosslinking agents.
Assembled proteins are in most cases not denatured (67,69-71). Enzymatic activity of glucose isomerase, glucoamylase, glucose oxidase, and peroxidase was preserved in multilayers with linear polyions comprising 20-30% as compared with free enzymes in solution. Moreover, in some cases the LbL immobilization with linear or branched polyions enhanced the enzymatic stability. The immobilization of proteins in multilayers preserves them from microbial attack. For example, the glucose oxidase/PEI multilayer was kept for 3 months in a refrigerator at 5°C, and it preserved 90% of its initial - enzymatic activity. Figure 5 shows a GOx/PEI multilayer film on a quartz crystal microbalance electrode. Furthermore, GOx in the multilayer with PEI was active up to 60°C, as compared with the 50°C GOx activity limit in solution (72). The pH profile of the GOx activity in the film became broad and shifted toward a higher pH than that of native GOx. The enzymatic activity of a GOx/PEI film increased linearly with the number of GOx layers for up to 10 protein layers, after which the film bioactivity became saturated. This saturation is probably due to substrate (glucose) diffusion limitations into the film since accessibiEty to the protein requires substrate transport through the multilayer.
Micropatterning
Micropatteming of biomolecules has important applications, including immunoassays,
<img file="IL190885A_D0054.tif" />
Fig. 5. Scanning electron microscope image of a film composed of (glucose oxidase/PDDA)18 on quartz crystal microbalance electrode.
chemical and biomedical sensors, drug screening, and tissue engineering. Microcontact printing (pCP) based on thiol compounds introduced by Whitesides et al. has been widely used to pattem self-assembled monolayers (SAMs) on gold surfaces (73,74). The patterns consisted of regions that encouraged protein adsorption or cell adhesion, alternated with regions that discouraged such interaction. However, the process required not only the use of metal coatings, but also alkanethiols or silanes as the ink.
A combination of traditional lithography and LbL assembly has been used to develop micropattems on a silicon wafer (9). The method can be compared to the micropatteming of a thiol compound on gold supports and further LbL assembly of multilayers (75). Both methods give patterns of approximately the same quality with clear support surfaces between the pattern
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Ai, Jones, and Lvov features, minimal feature sizes of approx 1-2 micron, and edge roughness of approx 0.1-0.2 micron. However,, the lithographic approach is compatible with existing silicon micromanufachiring technology. Thus, for industrial application one can use existing silicon technology to produce 4-inch diameter silicon wafers completely covered with needed patterns of nanoparticle LbL-multilayers (9). This may have important applications in biochips.
We have also directly patterned micro/nano structures on silicone rubber through the pCP method (11). A silicone rubber stamp with microchannel structures .was coated with polymer layers and microparticles through LbL assembly. Then coated materials were transferred onto an unmodified silicone rubber surface by contact printing. Patterning of carboxylated microspheres on silicone rubber resulted in well-defined micropattems. The resolution, stability, and accuracy of micro/nanosphere patterns correspond to the standard of the pCP technique. In Fig. 6,4.5-pm microsphere and 45-nm fluorescence nanoparticles patterns match the 60-|4m microchannels from the silicone rubber stamp. Later, polylysine/gelatin bilayers were further deposited on patterned microspheres .arid cell selective adhesion was observed (11). The patterned area with polylysine/gelatin was favorable for cells to adhere. While the unpattemed area is silicone rubber, which does riot support any cell adhesion. It is not clear which force was holding those pattemed negatively charged hydrophilic microspheres on the noncharged hydrophobic silicone surface. The mechanism of transfer is not clear, but the most probable explanation is that binding between the hydrophobic surface of silanized glass and proteins is stronger than the adhesion force between the proteins and the silicone rubber surface, as was suggested in (76).
NANO-ENCAPSULATION
OF MICRO/NANO-CORES
Assembly of charged polymers, lipid bilayers, proteins, and enzymes on 3-D micro/nan otemplates has potential applications in drug delivery, artificial cells, and bio/nanoreactors.
Drug Microcrystal and Protein Encapsulation
Advanced drug delivery systems have shown wide applications in the phannaceutical industry. Potential advantages of improved drug delivery include controllable drug level, reduced harmful side effects, decreased amount of drug, and improved patient compliance (77). Microencapsulation is an important method to control and target drug delivery. Biodegradable polymer-based particles can be prepared by interfacial polymerization or by phase separation from a polymer-solvent mixture (78-80). However, a number of common problems are associated with their fabrication, including polydispersity, uneven shell coverage, and core solidification. Whereas lipid liposomes have also been used as drug carriers (81), lipids can be deposited on LbL polymer shells and this lowers the permeability by a factor of 1000 for small molecules (82).
The LbL self-assembly technique is one of the nanotechnologies that has advanced the field of drug delivery (83). Drug microcrystals, proteins or enzymes can be directly encapsulated by polymer capsules and the rate of release can be adjusted through shell thickness. Fluorescein dye microcrystals were first used as a model system for controlled release studies (84). Polyanion PSS and polycation PAH were used to form a polyelectrolyte shell on the fluorescein core. Increasing the number of layers decreased the shell permeability and resulted in prolonged dye-core dissolution. Permeability decreased from 7 x 10<sup></sup> to 2 x 10<sup></sup>m/s as shell layers changed from 8 to 18. The permeability of fluorescein to a 20-run poly-, electrolyte multilayer is approx 10<sup>9</sup>־ m/3.
Polyelectrolyte multilayers were coated on drug microparticles through the LbL selfassembly technique for controlled release (15-16). Ibuprofen microcrystals sized between 5 and 40 micron have been encapsulated with polyelectrolytes, including chitosan, dextran
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<img file="IL190885A_D0055.tif" />
Fig. 6. Micropattems of (A) 4.5-gm microspheres and (B) 45-nm fluorescence nanoparticles on a silicone rubber substrate (scanning electron microscope image). (Scale bar: 60-μιη.) sulfate, carboxymethyl cellulose, and sodium alginate for controlled release (15). The release rate of ibuprofen from the microcapsules decreases as the shell thickness increases. Multilayers of (chitosan/dextran sulfate)10 achieved the longest release time, up to 3 times at pH 7.4 and 4 times at pH 1,4,. compared to bare ibuprofen microcrystals. Encapsulation of another drug microcrystal, furosemide, with gelatin/PSS multilayers resulted in prolonged release up to 300 times (16). These results show that variations in coating materials and num ber of layers can be used to control drug release time. LbL-based encapsulation has the following advantages over traditional methods of drug encapsulation: (1) the wall thickness and diameter of the microcapsule can be varied with a precision of a few nanometers; (2) the capsule wall architecture can be designed with different combinations of materials including polymers, lipid bilayers, and enzymes; (3) attachment of antibodies or antigens will allow targeting of capsules (14); (4) capsules can be made with diameters less than 1 micron, which
Cell Biochemistry and Biophysics
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Ai, Jones, and Lvov allows their use for injection; (5) compared to the polymer-based coacervation delivery systern, much less ballast material is required in the encapsulation procedure, ׳typically a polymer:drug ratio of 10:1 is used in the preparation of a polymer-based drug delivery system (85-86). In the LbL-shell approach studied here, the shell thickness of a capsule ranged from 55 to 125 nm, which is much smaller than the core (drug microcrystal) dimensions of approx 5x1x1 micron. The ratio of coating volume to drug volume is 1:4.
Protein or enzyme aggregates can also be covered through LbL encapsulation. Protein aggregates such as a-chymotrypsin were coated with PSS and PAH multilayers through LbL assembly (87). Only 3% of the encapsulated protein volume was released through three-layer polyelectrolyte shells in a pH 3 HCI solution at 4°C after 6 d. This preparation of microencapsulated a-chymotrypsin retained 73% active site content after 6 d of storage vs 43% for free enzymes. These results prove that assembly of a polyelectrolyte film onto protein aggregate templates is a simple technique for the preparation of enzymatic microcapsules that are stable in an acidic medium. Catalase 6-pm microcrystals were coated with- (PSS/PAH)5 shell, which provided enhanced catalytic activity Of this enzyme (109).
Polyelectrolyte Microshells
Microsized vehicles such as hollow polyelectrolyte shells (88-89), polymersomes (90), and colloidosomes (91) were introduced recently. These novel shells provide alternatives to traditional microvehicles, such as liposomes. Polymersomes with membranes at least 10 times less permeable than phospholipids bilayers have been made from amphiphilic diblock copolymers, but the size of a polymersome is not easily controlled. The most recently developed colloidosomes are size controllable but allow 0.1-pm diameter particles to penetrate freely, which is not favorable for drug delivery, Hollow polyelectrolyte shells assembled through LbL self-assembly allow precise control of shell size, wall thickness, materials, and permeability: Lipid bilayers, enzymes and nanoparticles can be included in linear polyion shells.
.Construction of hollow polyelectrolyte shells involves colloid-templated consecutive polyelectrolyte adsorption followed by decomposition of the templating core (88). The coating procedure of charged polyions on micro/nanosized melamine formaldehyde (MF) colloidal particles is illustrated in Fig. 1 (3-D assembly). The excess polyelectrolyte in solution can be washed before the next layer is deposited; After the desired polyelectrolyte layers are deposited, the coated particles are exposed to pH 1 HQ solution for core decomposition. Hollow shells can be obtained after washing (Fig. 7). In addition to MF particles, monodispersed 640-nm diameter polystyrene (PS) latex particles have been used as cores for hollow capsule formation (88-89), as well as inorganic cores such as. silica or MnCOj microcrystals.
Shell composition is predesigned and can contain charged polyions, biopolymers, lipid bilayers, and even magnetic nanoparticles. The shell thickness is adjustable through the number of coating layers. Customized shells can be fabricated by choosing appropriate materials and number of layers in assembly.The applications of hollow shells are typically drug or enzyme delivery, so understanding and controlling the shell permeability is important in membrane design. Permeability of small molecules can be measured indirectly through a 2-D diffusion model (92) or by means of fluorescence recovery after photobleaching (93). At 80°C, for a 2-pm-diameter capsule with a shell thickness of 10-nm, the diffusion coefficient (D) is 1.2 x 10~<sup>12</sup> cm<sup>2</sup> of PSS/PAH multilayers (93). The molecular weight cut-off for capsule wall permeation usually can be varied from 500 to 50,000 whereas small molecules and ions can readily diffuse through the capsule wall (94,95).
Shells can shift from an open state to a closed state by changes in environmental conditions such as temperature (93), pH (96-98), or presence of organic solvents (20). For the capsules made of PSS and PAH multilayers, the penetration of fluorescein is reduced by 3
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Layer-by-Layer Nano-Assembly
<img file="IL190885A_D0056.tif" />
Fig. 7. AFM image of 5-gm diameter (PSS/PAH)<sub>4</sub> hollow capsule.
orders of magnitude on heating at 80°C (93). The increased barrier is believed to be caused by annealing of holes, in the shell at the higher temperature, Currently, two loading mechanisms are used for (PSS/PAH)« shells; first, loading at low pH, and second, loading in a mixture of water and alcohol. Shells exposed to a pH 4.5 form holes of up to 10 nm in diameter (98). The pore opening and closing mechanisms are not fully understood, It is possible that changes of the polyelectrolyte charge upon pH variation induce pore formation (99) or loosen the polyelectrolyte network, thus enabling the polymer to penetrate (96). Shells incubated in a 1:1 mixture of water and ethanol are sufficiently permeable to allow penetration of 5-nm diameter urease globules through the shell membrane (20), (Fig. 8). When these same shells are transferred to water, urease is locked inside. A probable explanation is that the polyion network becomes segregated in the water/ethanol medium, allowing penetration of the urease, while the polyion walls relax to a
Cell Biochemistry and Biophysics closed structure when the capsules are returned to pure water.
Because shell permeability can be tuned by...
the above parameters, one can load drug or enzymes into the shell and preserve it in a closed state, Macromolecules such as proteins have been successfully loaded into hollow polyelectrolyte shells through pH-controlled and water/ethanol mixture-controlled methods. Temperature-controlled methods have not been used, despite the dramatic decrease in permeability caused by the annealing process, because the high temperature denatures encapsulated proteins.
Recently, enzymes such as a-chymotrypsin have been loaded into hollow alginate/protamine microsized capsules at pH 8 (100). The microcapsules possessed a high loading capacity, 10<sup>9</sup> protein molecules per microcapsule, which is 100 times higher than that of PSS/PAH shells loaded through the openingclosing״ mechanism (97). it is concluded that the cationic protein protamine can act as a
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Ai, Jones, and Lvov
<img file="IL190885A_D0057.tif" />
<img file="IL190885A_D0058.tif" />
In Water, closed
<img file="IL190885A_D0059.tif" />
Ethanoi/Water 1:1, open
<img file="IL190885A_D0060.tif" />
In \\ ater. ,Encapsulated
MM
Fig. 8. Permeation and encapsulation of urease-FITC into polyion multilayer capsules. Left, in water; middle, in water/ethanol mixture 1:1; right, the capsule with encapsulated urease again in water. Top, scheme; bottom, confocal fluorescence images of the capsules. (Reproduced with permission from Lvov, Y., Antipov, A. A., Mamedov, A., Mohwald, H., and Sukhorukov G. B. (2001) Urease encapsulation in nanoorganized microshells. Nano. Lett. 1, 125-128. Copyright 2001, American Chemistry Society.) crosslinking agent by formation of a complex with the alginate matrix (100). The a-chymotrypsin was retained inside the microcapsules for up to 24 h in water at pH 8. The protein release from the capsules can be adjusted by the alginate matrix properties (pore size, water content, stability etc.) and by the number of polyelectrolyte layers.
Artificial Cells
Microencapsulation of cells has applications in cell transplantation (101), cell-based drug delivery (102), and culture in bioreactors (103). The commonly used techniques for cell encapsulation are ionic gelation, interfacial precipitation, and complex coacervation. Multilayered microcapsules can give a better environment for cell functions than one layer encapsulation (104). As mentioned previously, the advantages of LbL self-assembly
Cell Biochemistry and Biophysics enable us to choose different biopolymers to control the capsule architecture.
Bovine platelets were coated with 78-nm silica nanoparticles, 45-nm fluorescent nanospheres, or bovine immunoglobulin G (IgG) through LbL assembly by alternate adsorption with oppositely charged linear polyions (14). Sequential deposition on platelet surfaces of cationic PDDA and anionic PSS was followed by adsorption of nanoparticles or immunoglobulins. A platelet coated with the shell of [PDDA/PSS/PDDA + (silica/PDDD)<sub>2</sub>] is viewed under transmission electron microscope (Fig. 9). Bovine IgG was assembled on platelets, as verified with anti-bovine IgGFITC labeling. Localized targeting of anti-IgG shelled platelets was also demonstrated. Live platelets, after encapsulation with polyion layers, can still respond to environmental signals (105). Erythrocyte and echinocyte cells were also coated with polyion shells (106).
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Layer-by-Layer Nano-Assembly
<img file="IL190885A_D0061.tif" />
Fig. 9. A bovine platelet covered with 78-iun silica nanoparticles (transmission electron microscopy image). (Reproduced with permission from Ai, H., Fang, M., Jones, S. A., and Lvov, Y. (2002) electrostatic layer-by-layer nanoassembly on biological microtemplates. Platelets Biomacromolecules 3, 560-564. Copyright 2002, American Chemistry Society.)
These results show that polymers, riarioparticles, and antibodies can be assembled on cell surfaces through LbL self-assembly. The coating of blood cells with nano-organized shells may have applications in cardiovascular research and targeted drug delivery.
Nanobioreactors
Nanobioreactors consist of nano-sized particles with biological (usually enzymatic) activity. Ordered enzyme (GOx, or urease)/polyion shells have been assembled on 400-nm diameter latex through LbL self-assembly (12,13,107, 108). Enzymatic activity was increased with the number of enzyme layers. Precoating the latex spheres with 40-run silica nanoparticles enhanced both the stability and enzymatic activity of the enzyme multilayers. The inclusion of silica layers on latex yields a higher surface area and roughness, adsorbing more enzymes and thereby increasing the catalytic activity of the nanoreactors. The incorporation of magnetic nanoparticles in these nanobioreactors introduces the possibility for self-stirring, which also enhances the effectiveness of the nanoreactor (13). Figure 10 shows a 420nm latex particle covered with a shell including (PEI/PSS) + (PEI/12-run magnetite)2 + (PEI/GOx)<sub>2</sub>.
DISCUSSION
Most polymers used in LbL assembly cannot be used in clinical , applications because they lack biocompatibility. The charged polymer PAH is not biocompatible, while it has been used mainly in constructing the hollow shells and in controlling drug release from capsules (15). Protein multilayers, usually composed of a protein layer and an alternative non-biocompatible polymer layer (e.g., PSS, PEI, PAH), are inappropriate to modify the surface of a medical device for in vivo purpose.
Samples prepared through LbL assembly were used in vitro. In vivo stability and biocompatibility tests will be useful to expand the biomedical applications.
Micropatterning of antigens or antibodies will be useful for clinical applications in fast and easy diagnosis of certain diseases. The inkjet printing of multilayered polyions is helpful for future applications.
Although controlled release of drugs and enzymes has been achieved through shell encapsulation, the total release time is still short compared to traditional polymer- or liposomebased drug delivery systems. Annealing of shells at higher temperatures could be effective to reduce the permeability dramatically (93). Thicker and crosslinked shells may be practical in design of long-term drug release carriers.
Bovine platelets were alive and able to respond to external signals after encapsulated with polyion shells, but the in vivo test still needs to be examined. Adding lipids on cell encapsulation may provide biocompatibility and can be applied to other cell types.
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Ai, Jones, and Lvov
<img file="IL190885A_D0062.tif" />
Hg. 10. A420-nm latex particle is covered with a shell including {(PEI/PSS) + (PEI/12-nm magnetite)<sub>2</sub> + (PEI/GOx)<sub>2</sub> (scanning electron microscope image). (Reproduced with permission from Fang, M., Grant, P. S., McShane, M., Sukhorukov, G., Golub, .V., and Lvov, Y. (2002) Magnetic bio/nanoreactor with multilayer shells of glucose oxidase and inorganic nanoparticles. Langmuir 18, 6338-6344. Copyright 2002, American Chemistry Society.)
Encapsulating functional enzymes inside biocompatible shells gives their enhanced stability and. allows additional׳ features (like inclusion to the shell of lipid bilayers, integral channel forming proteins or immunoglobulins for targeting).
CONCLUSIONS
An electrostatic LbL self-assembly technique has been used to successfully coat ultrathin films on different flat surfaces and onto microcores. The film architecture is precisely designed and can be controlled at nanometers through fabrication parameters. Hundreds of compounds, such as polypeptides, polysaccharides, proteins, synthetic polyions and nanoparticles, can be used in LbL assembly. With this simple technique, one can deposit 5- to 1000-nm thick films on large surfaces, such as slides, eye lenses, and surgical instruments, or micro/nano-scale objects, such as single cells,
Cell Biochemistry and Biophysics microbes, and viruses. This coating may provide surface biocompatibility or may protect large tissue'areas. LbL assembly on tiny cores (micro/nanotemplates) allows physicalchemical (nonbiologic) replication of biologic micro-organelles and design of polymeric microcapsules that can be loaded with drugs or enzymes. The small diameter of these micro/nanocapsules (100 nm to 10 pm) allows their targeting to specific locations in the body (and even to individual diseased cells) through antigen-antibody binding.
ACKNOWLEDGMENT
We are thankful for NSF-0210298 and NIH1RO1 EB00739-01 grants supporting this work. Any opinions, finding, and conclusions or recommendations expressed in this material are those of the authors and do not necessarily reflect the view of the National Science Foundation or National Institute of Health.
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Support of Louisiana Board of Regents with grant 2002/05-RDA-19 is acknowledged.
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72. Onda, M., Ariga, K., and Kunitake, T. (1999) Activity and stability of glucose oxidase in molecular films assembled alternately with polyions. J. Bioscl. Bioeng. 87, 69-75.
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82. Moya, S., Donath, E., Sukhorukov, G. B., et al.
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86. Dubin, P., Block, J., Davies, R., Schulz, D., Thies, C., eds. (1995) Macromolecular Complexes in Chemistry and Biology. Springier-Verlag, Berlin, pp. 285-324.
87. Balabushevitch, N. G., Sukhorukov, G. B., Moroz, N. A., et al. (2001) Encapsulation of proteins by layer-by-layer adsorption of polyelectrolytes onto protein aggregates: factors regulating the protein release. Biotechnol. Bioeng. 76(3), 207-213.
88. Donath, E., Sukhorukov, G. B., Caruso, F., Davis, S. A., and MShwald, H. (1998) Novel hollow polymer shells by colloid-templated assembly of polyelectrolytes. Angew. Chem. Int. Ed. 37(16), 2201-2205.
89. Caruso, H, Caruso, R. A., and Mohwald, H. (1998) Nanoengineering of inorganic and hybrid hollow spheres by colloidal templating. Science 282,1111-1114.
90. Discher, Β. M., Won, Y., Ege, D. S., Lee, J., Bates, F. S., Discher, D. E., and Hammer, D. A. (1999) Polymersomes: tough vesicles made from diblock copolymers. Science 284,1143-1146.
91. Dinsmore, A., Hsu, M., Nikolaides, M., Marquez, M., Bausch, A., and. Weitz, D. (2002) Colloidosomes: selectively permeable capsules composed of colloidal particles. Science 298, 1006-1009.
92. Klitzing, R. V. and Mohwald, H. (1996) A realistic diffusion model for ultrathin polyelectrolyte films. Macromolecules 29,6901-6906.
93. Ibarz, G.<sub>׳</sub> Dahne, L., Donath, E., and Mohwald, H. (2002) Controlled permeability of polyelectrolyte capsules via defined annealing. Chem. Mater. 14,4059-4062.
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97. Tiourina, O״ Antipov, A., Sukhorukov, G., Larionova, N., Lvov, Y., and Mohwald, H.
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98. Antipov, A. A., Sukhorukov, G״ Leporatti, S., Radtchenko, 1., Donath, E., and Mohwald, H.
(2002) Polyelectrolyte multilayer capsule permeability control. Colloid Surface A. 198-200 535-541
99. Mendelson, J., Barret, C., Chan, V., Pal, A., Mayes, A., and Rubner, M. (2000) Fabrication of microporous thin films from polyelectrolyte multilayers. Langmuir 16,5017-5023.
100. Tiourina, O. and Sukhorukov, G. (2002) Multilayer alginate / protamine microsized capsules: encapsulation of a-chymotrypsin and controlled release study. Inf. J. Pharmacol. 242,155-161.
101. Bruni, S. and Chang, T. (1989) Hepatocytes immobilised by microencapsulation in artificial cells: effects on hyperbilirubinemia in Gunn rats. Biomater. Artif. Cells. Artif. Organs 17,403-411.
102. Fremond, B., Joly, A״ Desille, M., Desjardins, J., Campion, J., and Clement, B. Cell-based therapy of acute liver failure: the extracorporeal bioartificial liver. Cell. Biol. Toxicol. 12,325-329.
103. Bader, A., Knop, E., Boker, K., et al. (1995) A novel bioreactor design for in vitro reconstruction of in vivo liver characteristics. Artif. Organs 19,368-374.
104; Chia, S., Wan, A., Quek, C״ et al. (2002) Multilayered microcapsules for cell encapsulation. Biomaterials 23, 849-856.
105. Ai, H., Fang, M., Lvov, Y, Mills, D., and Jones, S. Applications of the electrostatic layer-bylayer self-assembly technique in biomedical engineering. Proceedings of the Second Joint EMBS/BMES Conference, Houston, TX, 2002, pp. 502,503.
106. Neu B, Vbigt A, Mitlohner R, et al, (2001) Biological cells as templates for hollow microcapsules. J. Microencapsul. 18,385-395.
107. Caruso, F. and Schuler, C. (2000) Enzyme multilayers on colloid'particles: assembly, stability, and enzymatic activity. Langmuir 16,9595-9603.
108. Sukhorukov, G. Designed nano-engineering polymer films on coBoid al particles and capsules. In: Novel Methods to Study Interfacial Layers. (Mdbius, D., Miller, R., eds.). Elsevier, Amsterdam, 2001, pp. 384-416.
109. Caruso, E, Thau, D״ Mohwald, H., and Renneberg, R. (2000) Enzyme encapsulation in layer-by-layer engineered polymer multilayer capsules. Langmuir 16, 1485-1488.
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<img file="IL190885A_D0063.tif" />
(19) World Intellectual Property Organization
International Bureau (43) International Publication Date
December 2003 (04.12.2003)
IIIIIIIHIIIIIIIIW (10) International Publication Number
WO 03/099835 Al
PCT (12) INTERNATIONAL APPLICATION PUBLISHED UNDER THE PATENT COOPERATION TREATY (PCT) (51) International Patent Classification<sup>7</sup>: C07H 1/00,
3/00, 5/06, 5/10, 15/18 (21) International Application Number: PCT/US03/15901 (22) International Filing Date: 21 May 2003 (21.05.2003) (25) Filing Language: English (26) Publication Language: English (30) Priority Data:
60/382,512 21 May 2002 (21.05.2002) US (71) Applicant (for all designated States except US). EMORY UNIVERSITY [US/USJ; 1784 North Decatur Road, First Floor, North Decatur Building, Suite 130, Atlanta, GA 30322 (US).
(72) Inventors; and (75) Inventors/Applicants (for US only): CHA1KOF, Elliot,
L. [US/USJ; 150 Wicksford Glen, Atlanta, GA30350(US). SUN, Xue-Long [CN/USJ; 1548E Woodlake Drive, Atlanta, GA 30329 (US).
(74) Agents: WINNER, Ellen, P. et al.; Greenlee, Winner and Sullivan, P.C., 5370 Manhattan Circle, Suite 201, Boulder, CO 80303 (US).
(81) Designated States (national): AU, CA, JP, US.
(84) Designated States (regional): European patent (AT, BE, BG, CH, CY, CZ, DE, DK, EE, BS, Fl, FR, GB, GR, HU, IE, IT, LU, MC, NL, PT, RO, SE, SI, SK, TR).
Published:
— with international search report
For two-letter codes and other abbreviations, refer to the Guidance Notes on Codes andAbbreviations appearing at the beginning of each regular issue of the PCT Gazette.
WO 03/099835 Al llllllllllllllllllllllllllligilllllllllllilllH (54) Title: MULTIVALENT POLYMERS WITH CHAIN-TERMINATING BINDING GROUPS (57) Abstract: Polymeric molecules including glycopolymcrs useful for biomolccular recognition processes are provided comprising anchoring groups by which they can be immobilized onto surfaces. These molecules are easily synthesized. They are broadly described as molecules comprising a polymer backbone with pendent multivalent groups attached to the polymer backbone and an anchoring group attached to the polymer backbone for covalently or noncovalently attaching the molecule to a surface or another molecule. Such polymeric molecules can be attached to other molecules or surfaces to provide a wide range of bioactive materials. In addition, this invention provides suliated glycopolymers which are uselul for reducing blood coagulation, stimulating growth factors to bind to their receptors, stimulating cell proliferation and preventing degradation of soluble growth factors under conditions of low pH, heat, and proteolytic enzymes.
WO 03/099835 PCT/US03/15901
MULTIVALENT POLYMERS WITH CHAIN-TERMINATING BINDING GROUPS
CROSS-REFERENCE TO RELATED APPLICATIONS
This application claims priority to U.S. Application No. 60/382,512 filed May 21, 2002, which is incorporated herein by reference to the extent not inconsistent herewith.
BACKGROUND
Cell surface proteoglycans and glycolipids collectively form a membranebound carbohydrate coating, often referred to as a glycocalyx. Membrane-associated polysaccharides are critical mediators of molecular recognition events via the interactions of unique oligosaccharide sequences with specific protein epitopes that maybe found on bacteria, viruses, and other cells, as well as on a variety of soluble and matrix-bound factors. (Wang, D. et al., Nat. Technol. 2002, 20, 275-281; Houseman, B.T. and Mrksich, M., Chem. Biol. 2002, 9,443-454; Bryan, M.C. et al., Chem. Biol. 2002, 9, 713-720; Sun, X.L. et al., J. Am. Chem. Soc. 2002, 124, 72587259; Sackmann, E., Science 1996, 271,43-48.)
Fundamental studies of glycopolymer properties have provided insight regarding carbohydrate-mediated biomolecular recognition processes that may be attributed, in part, to a multivalent or cluster effect. (Bovin, N.V. and Gabius, H. J., Chem. Soc. Rev. 1995,413-421; Roy, R., Trends Glycosci. Glycotechnol. 1996, 8, 7999; Kiessling, L.L. et al., Curr. Opin. Chem. Biol. 2000,4, 696703־; Bertozzi C. R. and Kiessling, L.L., Science 2001, 291, 2357-2364.) Significantly, these efforts hold relevance for both pharmaceutical and biomaterial applications. For example, recent investigations have synthesized glycopolymers with surface anchoring groups located along the polymer backbone to generate glycosurfaces with potential utility in bioand immunochemical assays (Roy, R. et al., Chem. Soc., Chem. Commun. 1992, 16111613; Thoma, G. et al., J. Am. Chem. Soc. 1999,121, 5919-5929) as well as biocapture analysis. (Bundy, J.L. and Fenselau, C. Anal. Chem. 2001, 73, 751-757.)
Polymers with biotinylated end groups have been used to generate selforganizing protein-polymer hybrid amphiphiles (Hannink, J.M. et al., Angew Chem.
WO 03/099835
Int. Ed. 2001, 40, 4732-4735) as well as molecularly-engineered surfaces. (Cannizzaro, S.M. et al., Biotechnol. Bioeng. 1998, 58:529-535. Black, F.E. et al., Langmuir 1999,15, 3157-3161.) Biotin and streptavidin activation techniques have played an important role in the development of biofunctionalized surface for sensor or biomaterial applications. (Yang, Z. et al., Langmuir 2000,16:7482-7492; Hyun, J. et al., Langmuir 2001,17:6358-6367.) Characteristically, these chain-end functionalized polymers are prepared by further modification or conversion in several steps after initial polymer synthesis. (Hawker, C.J. and Hedrick, J.L. Macromolecules 1995, 28:2993-2995; Rodlert, M. et al., J. Polym. Sci. Polym. Chem. 2000, 38:47494763; Harth, E. et al., Macromolecules 2001, 34:3856-3862.)
The formation of a stabilized, membrane-mimetic film on a polyelectrolyte multiplayer (PEM) by in situ photopolymerization of an acrylate-functionalized phospholipid assembly at a solid/liquid interface was described in Marra, K.G. et al., Langmuir 1997,13, 5697-5701; Orban, J.M. et al., Macromolecules 2000, 33, 42054212; and Liu, H. et al., Langmuir 2002,18,1332-1339.
All patent applications and publications referred to herein are incorporated by reference to the extent not inconsistent herewith.
Polymers useful for biomolecular recognition processes which can be immobilized onto surfaces, and which are easily synthesized are needed.
SUMMARY OF THE INVENTION
This invention provides polymers, including glycopolymers, useful for biomolecular recognition processes which can be immobilized onto surfaces and which are easily synthesized.
Such polymers are broadly described as molecules comprising a polymer backbone; with pendent multivalent groups attached to the polymer backbone; and an anchoring group attached to the polymer backbone for covalently or noncovalently attaching the molecule to a surface or another molecule.
WO 03/099835
Such molecules may be represented by the following structural formula:
<img file="IL190885A_D0064.tif" />
A preferred embodiment is:
<img file="IL190885A_D0065.tif" />
II
This invention provides a wide range of molecules having anchoring groups, e.g., any moiety that can be biotinylated can be immobilized onto an avidin/streptavidin surface.
The polymer backbone may be straight or branched, saturated or unsaturated. For example, it may be prepared by polymerization of a glycomonomer having a polymerizable functionality such as acryloyl, methacryloyl or vinyl and acrylamide or methacrylamide.
The pendent multivalent group is preferably a saccharide, such as a monosaccharide, disaccharide, trisaccharide or oligosaccharide. Such saccharides may be sulfated, i.e., one or more OH moieties are replaced by SO3. Embodiments of this invention include as the saccharide N-acetyl-D-glucosamine, 0׳- and /3-N-acetylD-glucosamine-(l-4)-/3-D-glucuronic acid, pyranosides, lactose, and/or polylactose.
WO 03/099835
The pendent multivalent group may also be glycosaminoglycan, sialic acid, siayl Liews X, heparin, and/or oligopeptides.
These molecules preferably have a polydispersity index (molecular weight Mw/molecular number Mn) between about 1.1 and about 1.5 and have between about 2 and about 1000 pendent multivalent groups.
The molecules preferably also comprise a spacer arm between the anchoring group and the polymer backbone. The spacer arm may be alkyl, or alkenyl, such as C3-C9, and may comprise a ring, such as an aryl or cycloalkyl ring. The spacer arm may also comprise arylamide, methacrylamide, acryloyl, methacrylol, and vinyl. As is understood by those of skill in the art, the aryl ring (preferably a phenyl ring) or cycloalkyl ring of the foregoing molecules may have additional substituents which do not interfere with use of the compounds as described herein, and hydrogens in the above molecules may be replaced with groups such as methyl, ethyl, other lower alkyl groups, amine, sulfur, nitrogen, phosphorus and other atoms and groups which do not interfere with the use of the compounds as described herein, and oxygen can be substituted for sulfur in the above molecules. Further, the C-C-C-C carbon chains of the anchoring group, e.g., the biotin and biotin-cap molecules, may be longer or shorter, e.g., 2 to 8 carbons, and may contain additional pendent oxygens, amines, lower alkyl or other groups. Such rings may comprise at least one substituent which, depending on the electronic and steric effects of any substituent present, as is known to the art, may be ortho, meta or para, to the position at which the ring attaches to the polymer backbone. Ring substituents can be hydrocarbyl. Particular substituents are, e.g., methoxy, alcohol, ether, amine, polyamine, sulfate, phosphate, nitrate, nitrite, halogen selected from the group consisting of chlorine, bromine and iodine, salts of the foregoing, and other substituents which do not interfere with formation of the polymer via free radical polymerization. Preferably the substituent is a para substituent. Rings include 5-, 6-, or 7-membered rings, saturated or unsaturated.
The term hydrocarbyl is used herein to refer generally to organic groups comprised of carbon chains to which hydrogen and optionally other elements are attached. CH<sub>2</sub> or CH groups and C atoms of the carbon chains of the hydrocarbyl may be replaced with one or more heteroatoms (i.e., non-carbon atoms). Suitable
WO 03/099835 PCT/US03/15901 | heteroatoms include but are not limited to O, S, P and N atoms. The term hydrocarbylI includes, but is not limited to, alkyl, alkenyl, alkynyl, ether, polyether, thioether,I ascorbate, aminoalkyl, hydroxylalkyl, thioalkyl, aryl and heterocyclic aryl groups,I amino acid, polyalcohol, glycol, groups which have a mixture of saturated and| unsaturated bonds, carbocyclic rings and combinations of such groups. The term also includes straight-chain, branched-chain and cyclic structures or combinations thereof.
Hydrocarbyl groups are optionally substituted. Hydrocarbyl substitution includes substitution at one or more carbons in the group by moieties containing heteroatoms. Suitable substituents for hydrocarbyl groups include but are not limited to halogens, including chlorine, fluorine, bromine and iodine, OH, SH, NH, ΝΉ2, COH, CO2H, ׳
ORa, SRa, NRaRb, C0NRaR<sub>b</sub>, where R<sub>a</sub> and R<sub>b</sub> independently are alkyl, unsaturated1 alkyl or aryl groups, sulfate, sulfite, phosphate, nitrate, carbonyl, and polyamine.
The term amine refers to a primary, secondary, or tertiary amine group. A “polyamine” is a group that contains more than one amine group. A “sulfate” group is| a salt of sulfuric acid. Sulfate groups include —SO3, the group (SO4)<sup>2</sup> and sulfate radicals. “Phosphates” contain the group PO<sub>4</sub><sup>3</sup>־. “Glycols” are groups that have two alcohol groups per molecule of the compound.
The term alkyl takes its usual meaning in the art and is intended to includef straight-chain, branched and cycloalkyl groups. The term includes, but is not limited i to, methyl, ethyl, n-propyl, isopropyl, n-butyl, sec-butyl, isobutyl, tert-butyl, n-pentyl, neopentyl, 2-methylbutyl, 1-methylbutyl, 1-ethylpropyl, 1,1-dimethylpropyl, n-hexyl,
1-methylpentyl, 2-methylpentyl, 3-methylpentyl, 4-methylpentyl, 3,3-dimethylbutyl, 2,2-dimethylbutyl, 1,1-dimethylbutyl, 2-ethylbutyl, 1-ethylbutyl, 1,3-dimethylbutyl, n-heptyl, 5-methylhexyl, 4-methylhexyl, 3-methylhexyl, 2-methylhexyl, 1methylhexyl, 3-ethylpentyl, 2-ethylpentyl, 1-ethylpentyl, 4,4-dimethylpentyl, 3,3dimethylpentyl, 2,2-dimethylpentyl, 1,1-dimethylpentyl, n-octyl, 6-methylheptyl, 5methylheptyl, 4-methylheptyl, 3-methylheptyl, 2-methylheptyl, 1-methylheptyl, 1ethylhexyl, 1-propylpentyl, 3-ethylhexyl, 5,5-dimethylhexyl, 4,4-dimethylhexyl, 2,2diethylbutyl, 3,3-diethylbutyl, and 1-methyl-1-propylbutyl. Alkyl groups are | optionally substituted. Lower alkyl groups are C!-C6 alkyl and include among others ί methyl, ethyl, n-propyl, and isopropyl groups.
The term cycloalkyl refers to alkyl groups having a hydrocarbon ring, preferably to those having rings of 3 to 7 carbon atoms. Cycloalkyl groups include I those with allcyl group substitution on the ring. Cycloalkyl groups can include straight-chain and branched-chain portions. Cycloalkyl groups include but are not
WO 03/099835 limited to cyclopropyl, cyclobutyl, cyclopentyl, cyclohexyl, cycloheptyl, cyclooctyl, and cyclononyl. Cycloalkyl groups can optionally be substituted.
The term unsaturated alkyl group is used herein generally to include alkyl groups in which one or more carbon-carbon single bonds have been converted to carbon-carbon double or triple bonds. The term includes alkenyl and alkynyl groups in their most general sense. The term is intended to include groups having more than one double or triple bond, or combinations of double and triple bonds. Unsaturated alkyl groups include, without limitation, unsaturated straight-chain, branched or cycloalkyl groups. Unsaturated alkyl groups include without limitation: vinyl, allyl, propenyl, isopropenyl, butenyl, pentenyl, hexenyl, hexadienyl, heptenyl, cyclopropenyl, cyclobutenyl, cyclopenteriyl, cyclopentadienyl, cyclohexenyl, cyclohexadienyl, 1-propenyl, 2-butenyl, 2-methyl-2-butenyl, ethynyl, propargyl, 3methyl-1-pentynyl, and 2-heptynyl. Unsaturated alkyl groups can optionally be substituted.
Substitution of alkyl, cycloalkyl and unsaturated alkyl groups includes substitution at one or more carbons in the group by moieties containing heteroatoms. Suitable substituents for these groups include but are not limited to OH, SH, NH<sub>2</sub>, COH, CO2H, ORc, SRc, P, PO, NRcRd, CONRcRd, and halogens, particularly chlorines and bromines where Rc and Rd, independently, are alkyl, unsaturated alkyl or aryl groups. Preferred alkyl and unsaturated alkyl groups are the lower alkyl, alkenyl or alkynyl groups having from 1 to about 3 carbon atoms.
The term aryl is used herein generally to refer to aromatic groups which have at least one ring having a conjugated pi electron system and includes without limitation carbocyclic aryl, aralkyl, heterocyclic aryl, biaryl groups and heterocyclic biaryl, all of which can be optionally substituted. Preferred aryl groups have one or two aromatic rings.
Aryl groups may be substituted with one, two or more simple substituents including, but not limited to, lower alkyl, e.g., methyl, ethyl, butyl; halo, e.g., chloro, bromo; nitro; sulfato; sulfonyloxy; carboxy; carbo-lower-alkoxy, e.g., carbomethoxy, carbethoxy; amino; mono- and di-lower-alkylamino, e.g., methylamino, ethylamino, dimethylamino, methylethylamino; amido; hydroxy; lower-alkoxy, e.g., methoxy, ethoxy; and lower-alkanoyloxy, e.g., acetoxy.
WO 03/099835
Carbocyclic aryl refers to aryl groups in which the aromatic ring atoms are all carbons and includes without limitation phenyl, biphenyl and naphthalene groups.
Aralkyl refers to an alkyl group substituted with an aryl group. Suitable aralkyl groups include among others benzyl, phenethyl and picolyl, and may be optionally substituted. Aralkyl groups include those with heterocyclic and carbocyclic aromatic moieties.
Heterocyclic aryl groups refers to groups having at least one heterocyclic aromatic ring with from 1 to 3 heteroatoms in the ring, the remainder being carbon atoms. Suitable heteroatoms include without limitation oxygen, sulfur, and nitrogen. Heterocyclic aryl groups include among others furanyl, thienyl, pyridyl, pyrrolyl, Nalkyl pyrrolo, pyrimidyl, pyrazinyl, imidazolyl, benzofuranyl, quinolinyl, and indolyl, all optionally substituted.
The molecules of this invention may comprise hydrophobic and hydrophilic substituents as is known to the art.
The anchoring group may be any group which facilitates conjugation of the foregoing molecules to surfaces or other molecules, such as any group allowing covalent binding to a binding partner, or noncovalent binding to another molecule or surface. The anchoring group is preferably selected from the group consisting of biotin, biotin-cap, charged anchoring groups such as styrene sulfate, styrene sulfonate, alkyl sulfate, alkyl sulfonate, and alkyl sulfonic acid; chemically-reactive groups such as thiols, amines, aldehydes and carboxylic acids, photocrosslinkable groups such as aryldiazirine and arylazide, and hydrophobic groups such as C6-C22 alkyl, C12-C22 lipid or C12-C22 phospholipid. The term “lipid” herein includes phospholipids.
The molecule preferably comprises a first pendent group comprising a linking group to connect it to the polymer backbone and a multivalent moiety connected to the linking group. The first pendent unit may comprise a hydrocarbyl-linking group connected to the backbone. Preferably the linking group contains about 3 to about 9 atoms, most preferably carbon atoms. It is preferably (CH2)<sub>n</sub> where n is 3 to 9, and preferably is a straight chain, but may also be an unsaturated and/or branched chain, may comprise additional moieties attached to the chain, and the chain may comprise hetfiroatoms, so long as formation of the polymer via free radical polymerization is
ך
WO 03/099835 not interfered with by such heteroatoms, branching, and/or substituents. When the first pendent unit is made using an alkenyl-based glycomonomer, this helps lower the polydispersity index, thus it is preferred that an alkenyl-based glycomonomer be used.
The molecule may also comprise a second pendent unit. The second unit consists of or comprises a lipid or long alkyl chain of about C7 to C30. Preferably the second pendent unit comprises about 3 to about 9 atoms. It may comprise substituents, branches, and hetero-atoms as does the linking group. It is preferably formed of an easily polymerizable hydrocarbyl monomer by copolymerization along with the first unit. Preferably the second unit is polymerized from acrylamide, acrylate, or alkenyl compounds, most preferably acrylamide. The molecules of this invention may comprise up to about 1000 of such second units. The second unit may function as a spacer, or it may be derived from an easily-polymerizable monomer that promotes polymerization during the process of making the molecules of this invention.
The first and second units may be interspersed with each other in random order along the polymer backbone. As is known to the art, polymerization process parameters such as concentration of reactants, and temperature, will determine the statistical frequency and order of the first and second units.
The number of pendent units may be up to about 2000. In one embodiment, the second pendent unit comprises or consists of phosphatidylcholine. When a second pendent unit is present, the sum of the number of multivalent moieties and second unit moieties is preferably no more than about 2000, more preferably no more than about 1000, and most preferably no more than about 100. The first and second units may be in cis-or trans- configuration with respect to each other. Consecutive first units may also be cis- or trans- to each other.
The first and second units may be interspersed with each other in random order along the polymer backbone. As is known to the art, polymerization process parameters, such as concentration of reactants and temperature, will determine the statistical frequency and order of the first and second units.
In certain embodiments of this invention, the molecule comprises a cyanoxyl group at the end of the polymer backbone opposite the anchoring group.
WO 03/099835
These molecules are useful for providing surfaces capable of binding to bioactive molecules for use in bio and immunochemical assays, as well as biocapture analysis. Bioactive molecules can include thrombomodulin, growth factors, cytokines, proteins, peptides, cells, viruses, antibodies, fluorescent groups, FAB fragments, IgG, catalysts, ligand molecules for capture of other molecules, etc., as is known to the art. These molecules may also be used to target specific bioactive molecules in drug delivery methods. Activated surfaces, comprising such bioactive molecules bound to the multivalent groups of the molecules of this invention, are also provided herein.
This invention also provides a bioactive surface comprising the foregoing molecules covalently or non-covalently bound to the surface via the anchoring group. Such surfaces may be any surface known to the art to which it is desired to impart biological functional properties, e.g., metal, glass, silicon, synthetic polymers, natural polymers such as alginate and collagen, surfaces of medical devices in contact with blood or tissue such as vascular grafts, catheters, and biosensors, and membrane mimetic surfaces. PCT publications WO98/16198, WO 00/00239, WO 01/78800, WO 02/055021 and WO 02/09647, and U.S. Application No. 60/428,438 describe membrane-mimetic materials and polymers useful for binding to bioactive molecules which are useful in the practice of this invention. All these reference are incorporated herein by reference to the extent not inconsistent herewith. Definitions of terms used in said references apply hereto unless application of such definitions would result in inconsistency or loss of meaning, in which case, explicit or implicit definitions used herein apply to the disclosure hereof. Such membrane-mimetic surfaces include glycocalyx-mimetic surfaces, supported lipid surfaces, and polyelectrolyte multilayers. A supported lipid surface is defined as a single continuous phospholipid bilayer on a solid or polymeric surface. A polyelectric multilayer is defined as a surface made by electrostatic self-assembly of polyelectrolytes, also referred to as layer-by-layer assembly of polyelectrolytes . In one embodiment, the surface is made up of an elastic polypeptide block copolymer having hydrophilic and hydrophobic groups.
ו
Surfaces for binding to the molecules of this invention can be prepared by immobilizing a binding partner for an anchoring group of this invention onto a solid
WO 03/099835 polymeric surface by covalent or non-covalent binding. Examples are acid- or Biotinmodified PET surfaces, or biotin, biotin-lipid modified silicon, glass or medical device surfaces.
This invention also comprises the foregoing molecules covalently bound via their anchoring groups to appropriate binding partners such as avidin, streptavidin, an amine-containing group which links via —OCN by isourea bond formation such as a protein, a polypeptide, a polymer, a dendrimer, or a lipid.
In one embodiment, two, three or four of the molecules of this invention may be bound to the same binding partners via their anchoring groups to make dimers, trimers, and tetramers. Such complexes are useful for binding to bioactive molecules such as antigens, to provide a higher cluster density of antigenic pendent moieties, to improve antigenicity and circulating half-life. Such molecules are also useful to carry targeting groups attached to the multivalent portions of one or more portions of the molecule and other bioactive molecules such as toxins bound to other multivalent portions of the molecule.
The molecules of this invention may also be covalently or non-covalently bound to a biological marker known to the art such as an organic or inorganic fluorescent dye or nanoparticle.
Sulfated saccharide molecules of this invention are useful for a variety of biological purposes.
One embodiment of this invention provides a sulfated molecule designated SL3 having a molecular weight of about 9300 and a PDI of 1.46 which is a copolymer of sulfated lactose monomers and acrylamide at a molar ratio of acrylamide to sulfated lactose monomers of about 1:10 and a lactose content of about 57 wt%.
Such molecules are as effective as heparin in preventing coagulation of blood. Thus, this invention comprises reducing coagulation of blood by contacting the blood with an effective amount of a sulfated glycopolymer of this invention, preferably SL3.
WO 03/099835 PCT/US03/15901
These sulfated molecules are also useful for promoting binding of growth factors to their receptors and stimulating cell proliferation when an effective amount of such sulfated molecules, preferably heptasulfate disaccharides, and more preferably SL3, are placed in contact with cells which are responsive to growth factors. The sulfated molecules also selectively stimulate FGF-2 growth factor to its receptor, i.e., they do not stimulate FGF-1 binding.
The sulfated polymer molecules of this invention are also useful for preventing degradation, under conditions of heat, low pH and proteolytic enzymes, of soluble growth factors released into extra-cellular matrix when an effective amount of such sulfated polymer molecules, preferably sulfated saccharide molecules, and more preferably SL3, are placed in contact with growth factors such as FGF-2.
This invention also provides molecules having the following formula:
<img file="IL190885A_D0066.tif" />
ΠΙ wherein R is an anchoring group, and 0 represents a ring selected from the group consisting of aryl, aralkyl, cycloalkyl, cycloalkenyl, heterocyclic rings and substituted rings.
This invention further provides molecules having the following formula:
<img file="IL190885A_D0067.tif" />
IV wherein R is an anchoring group, and 0 represents a ring selected from the group consisting of aryl, aralkyl, cycloalkyl, cycloalkenyl, heterocyclic rings and substituted rings.
This invention further provides molecules having the following formula:
WO 03/099835
<img file="IL190885A_D0068.tif" />
<img file="IL190885A_D0069.tif" />
wherein R is an anchoring group; 0 represents a ring selected from the group consisting of aryl, aralkyl, cycloalkyl, cycloalkenyl, heterocyclic rings and substituted rings; x is between about 1 and about 50, preferably between about 5 and about 30 and more preferably between about 5 and about 12; y is between about 1 and about 100, preferably between about 50 and about 80; n is between about 1 and about 100, preferably between about 10 and 50; R1 is selected from the group consisting of monosaccharides, oligosaccharides, polysaccharides and glycosaminoglycans such as galactose, sialic acid, siayl Liews X, heparin, oligopeptides and other biomolecules, conjugated to -(CH2)m-HN-CO- which is conjugated to the polymer backbone; and wherein m is 1 to about 5.
This invention also provides methods of making the foregoing molecules comprising the steps of:
(a) providing a compound having the structure:
<img file="IL190885A_D0070.tif" />
VI wherein R is an anchoring group; and
O represents a ring selected from the group consisting of aryl, aralkyl, cycloalkyl, cycloalkenyl, heterocyclic rings and substituted rings;
(b) reacting said molecule of step (a) with HBF4 to form a molecule having the structure:
WO 03/099835 (c) reacting the molequle of step (b) with a cyanate to form a molecule having the structure:
© Θ .n=nbf<sub>4</sub>
III .OCN
VII (d) reacting the molecule of step (c) with a molecule having a multivalent moiety and a terminal vinyl group to form a compound having the formula:
r<sub>1</sub> conh<sub>2</sub> ‘2 where x is between about 1 and about 50, preferably between about 5 and about 30, and more preferably between about 5 and about 12;
y is between about 1 and about 100, preferably between about 50 and about 80;
n is between about 1 and about 100, preferably between about 10 and
50;
and R1 is selected from the group consisting of monosaccharides, oligosaccharides, polysaccharides and glycosaminoglycans such as galactose, sialic acid, siayl Liews X, heparin, oligopeptides and other biomolecules, conjugated to -(CH<sub>2</sub>)m-HN-CO- which is conjugated to the polymer backbone; and
WO 03/099835 wherein m is 1 to about 5.
The reaction mixture of step (d) may also include a comonomer comprising a vinyl group. The comonomer may be acrylamide, acrylate, C1-C10 alkenyl, and their derivatives. Derivatives include such groups having substituents which do not interfere with the reaction.
This invention also provides methods of growing the polymers of this invention having multivalent substituents directly on a surface by first attaching a molecule of Formula VI, VH or VIH to the surface and conducting the polymerization reactions in situ.
The molecules of this invention comprising multivalent groups may be covalently bound to bioactive moieties such as proteins, e.g., growth factors and cytokines, as well as viruses, cells and substrates, through the multivalent groups, as is known to the art with respect to carbohydrate-mediated biomolecular recognition processes. The end-product molecules of this invention are useful in protein separation, cell culture, and drug-delivery systems, as well as in targeting for treatment of wound healing and other pathological conditions.
These molecules are useful for providing surfaces capable of binding to bioactive molecules for use in bio and immunochemical assays, as well as biocapture analysis. Bioactive molecules can include thrombomodulin, growth factors, cytokines, proteins, peptides, cells, viruses, antibodies, fluorescent groups, FAB fragments, IgG, catalysts, ligand molecules for capture of other molecules, etc., as is known to the art. These molecules may also be used to target specific bioactive molecules in drug delivery methods. Surfaces with the foregoing molecules bound thereto, and also with bioactive molecules attached to the multivalent moieties of said molecules are also provided herein.
BRIEF DESCRIPTION OF THE FIGURES
Figure 1 is an <sup>l</sup>H NMR spectrum of the biotin terminated glycopolymer of Formula Π.
WO 03/099835
PCI7US03/15901
Figure 2 shows results of a streptavidin-biotin binding SDS-PAGE gel shift assay: (1) two equivalents of glycopolymer; (2) 20 equivalents of glycopolymer. A, marker; C, Streptavidin alone; D, streptavidin plus p-chlorophenyl-glycopolymer; E, streptavidin plus biotin-glycopolymer of Formula Π; F, streptavidin plus biotin-capglycopolymer of Fonnula II with biotin-cap substituted for biotin.
Figure 3 is a schematic representation of lectin binding to a glycopolymerderivatized surface.
Figure 4 is a schematic representation of a glycocalyx-mimetic thin film produced by coupling biotin-tenninated glycopolymers to a supported lipid membrane.
Figure 5 shows advancing and receding contact angles of successive assemblies of an alginate/poly-L-lysine (ALG/PLL) multilayer, terpolymer (TER), biotin-PE/PC lipid vesicles (B-PE/PC), streptavidin (STREP) and glycopolymer (GLY): Figure 5A shows results for 10 mol% biotin-PE; Figure 5B shows results for 25 mol % biotin-PE, and Figure 5C shows results for 50 mol% biotin-PE.
Figure 6 shows parallel (Rp)(I) and perpendicular (Rs)(II) polarized external reflection infrared spectra of polymerized films: 10 mol % biotin-PE/PC (Figure6A) 25 mol % biotin-PE/PC (Figure 6B); and 50 mol % biotin-PE/PC (Figure 6C). IR bands labeled with an asterisk in Rp polarized spectra indicate CH2 absorption modes that are changing in intensity with increasing biotin-PE content as shown in part I, spectra A-C.
Figure 7 shows parallel (Rp) (I) and perpendicular (Rs) (II) polarized external reflection infrared spectra of a polymerized 10 mol % biotin-PE/PC film (Figure 7A); spectra following successive absorption of streptavidin (Figure 7B); and a glycopolymer (Figure 7C). IR bands labeled with an asterisk in Rp polarized spectra indicate CHj absorption modes that are changing in intensity after streptavidin binding to the biotin-PE-functionalized surface as shown in part I, spectra A and B.
WO 03/099835
Figure 8 shows parallel (Rp) (I) and perpendicular (Rs) (Π) polarized external reflection infrared spectra of a polymerized 25 mol % biotin-PE/PC film (Figure 8A); spectra following successive absorption of streptavidin (Figure 8B) and a glycopolymer (Figure 8C). IR bands labeled with an asterisk in Rp polarized spectra indicate CH<sub>2</sub> absorption modes that are changing in intensity after streptavidin binding to the biotin-PE-functionalized surface as shown in part I, spectra A and B.
Figure 9 shows parallel (Rp) (I) and perpendicular (Rs) (Π) polarized external reflection infrared spectra of a polymerized 50 mol % biotin-PE/PC film (Figure 9 A); spectra following successive absorption of streptavidin (Figure 9B), and a glycopolymer (Figure 9C).
Figure 10 shows PTT dose-response study of glycopolymers bearing sulfated lactose units. Both Lovenox (LMW heparin) and heparin are included as positive controls. Significant prolongation of partial thromboplastin time (PTT) is observed with SL3, a sulfated lactose polymer of this invention.
Figure 11 shows [<sup>3</sup>H]thymidine incorporation into BaF3-FRlC-ll cells treated with 3 ng/mT, of growth factor FGF-2 and increasing concentrations of heparin or indicated test compounds.
Figure 12 shows the effect of heparin or sulfated lactose polymer SL3 (25 pg/mL) on the biological activity of heat-treated basic FGF.
DETAILED DESCRIPTION
Polymers and molecules of this invention comprise anchoring groups as means for binding to a surface to form a membrane-mimetic surface. Avidin (streptavidin)/biotin binding provides preferred means for binding said molecules. The molecules, polymers and surfaces of this invention have the advantage of being rapidly synthesized in a mild aqueous environment with simple washing and purification steps. Thus, potential damage to candidate surface ligand groups due to the conjugation process is limited.
WO 03/099835
This invention also provides stable, substrate-supported model membranes. Preferred membranes emulate the structural features of the glycocalyx. These model membranes and surface modification strategies are useful to enhance the functionality of biosensors, biochips, and microfluidic devices, and to improve the clinical performance characteristics of blood-contacting artificial organs and other implantable medical devices by modulating maladaptive processes at the bloodmaterial and tissue/material interfaces.
Membrane-bound carbohydrates can exert a steric repulsive effect that improves the specificity of biological interactions by limiting nonspecific cell/cell and protein/cell binding. Nonetheless, glycopolymers bearing a series of pendent anchoring groups characteristically demonstrate reduced bioactivity due to steric hindrance, which can be partially offset through the introduction of a spacer arm between the anchor and the polymer backbone.
Preferred embodiments of this invention are further described below. As will be apparent to those skilled in the art, other molecules, substituents, and reagents may be substituted for those disclosed herein to provide the molecules and surfaces as broadly described hereinabove.
The molecules in solution are in equilibrium with free cyanoxyl radicals which may leave the terminal end of the polymer backbone, leaving it free to participate in further polymerization reactions.
In one embodiment of the present invention, biotin chain-terminated polymers were synthesized bearing pendent lactose units. These glycopolymers were used to fabricate a glycocalyxlike structure on a membrane-mimetic film composed of mixed polymerizable lipids containing phosphatidylcholine or biotin headgroups (Figure 4). Polarized external reflection infrared spectroscopy in combination with confocal fluorescence microscopy was utilized to characterize the detailed molecular structure of this system and the uniformity of the thin film coating after streptavidin and glycopolymer binding. Biotinylated lipids appear to cluster in microdomains within the membrane-mimetic film, particularly at high surface density. Nonetheless, a
WO 03/099835 uniform carbohydrate coating was achieved after glycopolymer binding to the membrane-mimetic film.
In another embodiment, molecules of this invention were covalently bonded to a synthetic protein copolymer having selected plastic and elastic properties as described in U.S. Patent Application No. 60/428,438 filed November 22, 2002, incorporated herein by reference to the extent not inconsistent herewith. The surface is made of a protein copolymer comprising at least one hydrophilic block and at least one hydrophobic block, and up to three or more blocks. In one embodiment, the surface comprises a protein copolymer having a first end block, a second end block, and a middle block, wherein said first and second end blocks are substantially identical. In a preferred embodiment, the protein copolymer comprises hydrophobic end blocks and a hydrophilic middle block.
In a particular embodiment of this invention, the surface is made of an elastic polypeptide copolymer comprising a first and last end block which comprises a polypeptide encoded by a nucleic acid sequence of [VPAVG(IPAVG)4]n or a [(IPAVG)4(VPAVG)]n sequence, and the middle block comprises a polypeptide encoded by a nucleic acid sequence selected from the group consisting of: [(VPGEG) (VPGVG)4]<sub>m</sub> , [(VPGVG)4(VPGEG)]<sub>m</sub>, and (VPGVG)<sub>2</sub>VPGEG(VPGVG)<sub>2</sub>]<sub>m</sub>. In another embodiment, the surface is made of a protein copolymer which comprises endblocks selected from amino acid sequences encoded by the above endblock nucleotide sequences and a middle block selected from amino acid sequences encoded by the above middle block nucleotide sequences, n is from about 5 to about 100, and m is from about 10 to about 100. In a particular embodiment, n is about 16.
In another embodiment, the middle block is a polypeptide selected from the group consisting of polypeptides encoded by:
VPGVG [VPGVG(VPGIGVPGVG)2]19VPGVG;
VPGVG [(VPGVG)<sub>2</sub>VPGEG(VPGVG)<sub>2</sub>]3oVPGVG;
VPGVG [(VPGVG)2VPGEG(VPGVG)2]38VPGVG;
VPGVG [(VPGVG)2VPGEG(VPGVG)2]48VPGVG;
VPGVG [VPGVG(VPNVG)4]12VPGVG;
VPGVG [(APGGVPGGAPGG)2]23VPGVG;
WO 03/099835
VPGVG [(APGGVPGGAPGG)<sub>2</sub>]30VPGVG;
[VPGVG(IPGVGVPGVG)2] 19;
[VPGEG(VPGVG)4130;
[VPGEG(VPGVG)4]48;
[(APGGVPGGAPGG)2]22; and
[(VPGMG)5]<sub>x</sub>, wherein x is from about 10 to about 100.
These protein copolymers have elastic properties, i.e., are able to stretch from about 2.5 up to about 14 times their initial length.
Surfaces may be derivatized with binding groups such as streptavidin, which binds to biotin, by methods described in Example 2 below. Surfaces may also be prepared for binding to the molecules of this invention by derivatizing with other binding groups known to the art which bind to specific anchoring groups used in this invention.
A straightforward approach is provided to synthesize biotin chain-terminated glycopolymers of low polydispersity (Formulas I and II), via use of a biotinderivatized arylamine initiator employed in a cyanoxyl-mediated free radical polymerization scheme.
Example 1
A representative chain end-functionalized glycopolymer was designed as exemplified in Formula II and Figure 3 in which multivalent lactose units serve as ligands for lectins and/or antibodies, and a single biotin group provides an anchor by its specific binding activity to avidin or streptavidin. Modulating lactose density as well as polymer solubility was achieved by using acrylamide as a comonomer and a spacer arm (X) between biotin and the polymer backbone was used for further optimization of the polymer-avidin/streptavidin interaction. The synthetic strategy relies on our previously developed cyanoxylmediated free-radical polymerization process, in which arylamines have been identified as candidate initiators. (Grande, D. et al., Macromolecules 2000, 33,1123-1125; Grande, D. et al., Macromolecules 2001, 34,1640-1646.) Specifically, the biotin derivatized arylamine was used as an initiator
WO 03/099835 for cyanoxyl-mediated free radical polymerization of 2-acrylaminoethyl lactoside and acrylamide so as to provide the desired biotin chain-terminated glycopolymers for subsequent use in glycosurface engineering.
In the current study, 4-aminobenzyl-biotinamide was used wherein the biotin was biotin or biotin-cap:
Biotin
O
HN NH
VIII
<img file="IL190885A_D0071.tif" />
IX
These compounds were designed and investigated as initiators for the polymerization of 2-acrylaminoethyl lactoside with acrylamide. The biotin-containing arylamine initiator 4-aminobenzyl biotinamide was prepared by the condensation of commercial available p-nitrobenzylamine with TV-hydroxysuccinimidyl-biotin, and 7V-hydroxysuccinimidyl-biotinamidocaproate followed by hydrogenation with Pd-C in methanol in high yield, respectively, 2-Acrylaminoethyl lactoside was prepared from lactose per-acetate via four steps including glycosylation, hydrogenation, and acrylation with acryloyl chloride in 53% total yield.) Treatment of the 4-aminobenzyl-biotinamide with HBF4 and NaNO2 in deoxygened H2O-THF (1:1) gave the arenediazonium cation:
WO 03/099835
<img file="IL190885A_D0072.tif" />
Θ Θ n=nbf<sub>4</sub> which upon reaction with NaOCN at 50° C afforded the biotinyl aryl free radical:
.OCN and the cyanoxyl free radical (.OCtN) as the initiating system for copolymerization of glycomonomer 2-acrylaminoethyl lactoside and acrylamide. The biotin chainterminated glycopolymer:
XII was generated in 75% conversion as a white spongy powder. Similarly, using biotincap-arylamide as the initiating species, a glycopolymer was generated with a spacer arm between biotin and the polymer chain in 70% conversion. The resultant copolymers were characterized by NMR spectroscopy (Figure 1), as well as by sizeexclusion chromatography (SEC) coupled with both refractive index and laser-light scattering (LLS) detectors. Comparison of the integrated signal from the phenyl protons (7.10 ppm, H2’, 6’ and 7.18 ppm, H3’, 5’) with that due to the anomeric protons of lactose (4.36 ppm, Hl ’-Lact and 4.43 ppm, Hl ’-Lact), as well as that of the polymer backbone methine (2.10 ppm, CH) and methylene (1.55 ppm CH<sub>2</sub>), indicated an average polymer composition of 10 lactose and 70 acrylamide units. Notably, downfield shifts of H2’, H6’ phenyl protons (7.10 ppm) demonstrated C—C bond formation between the phenyl group and the polymer backbone. The actual molar mass (Mri) was 12 kDa with a polydispersity index (Mw/Mn) of 1.3 from SEC/RI/LLS for the compound of Formula XIII where R is biotin.
A gel shift assay was performed to verify streptavidin-glycopolymer binding in a solution-phase system. Streptavidin-glycopolymer complexes were generated as
WO 03/099835 illustrated in lanes E and F (Figure 2, Gel I) while not observed on incubation with a comparable glycopolymer lacking a biotin group [lane D]. Since each streptavidin (60 kDa) contains four identical subunits, a streptavidin band remains present when mixed with only 2 equivalents of biotin-glycopolymer (Gel I, Lanes E and F), but disappears in the presence of an excess of glycopolymer (Gel II, Lanes E and F). The retarded migration of streptavidin-glycopolymer complexes may be due to both an increase in molecular weight and a reduction in the capacity of the apolar portions of streptavidin to interact with the alkyl moiety of sodium dodecysulfate (SDS). (Weber, K. and Osborn, M., J. Biol. Chem. 1969, 244, 4406-4412.) In this system, the presence of a spacer arm did not have a measurable impact on glycopolymer/ streptavidin affinity.
Glycopolymer-coated surfaces (Figure 3) were produced by incubating streptavidin-derivatized PET membranes in a glycopolymer solution (1 mg/mL in PBS) for lh at room temperature. Membranes were subsequently washed with PBS and incubated in a solution of a FITC-labeled galactose binding lectin (1 mg of psophocarpus tetragonolobus/mL in PBS). Lectin binding was observed in regions of glycopolymer immobilization, while no such activity was noted in surface regions not derivatized with streptavidin.
Cyanoxyl-mediated free-radical polymerization with a biotin-derivatized arylamine initiator has been shown to provide a straightforward strategy for generating biotin chain-terminated glycopolymers. Streptavidin-biotin binding was verified by a SDS-PAGE gel shift assay and the fabrication of a glycocalyx-mimetic surface achieved.
Example 2
Further tests of fabrication of glycocalyx-mimetic surfaces were performed using a biotin chain-terminated glycopolymer which was incorporated onto streptavidin functionalized polymeric lipid films. By variation of carbohydrate type and density, the production of structurally heterogeneous surfaces is facilitated. Significantly, increasing the surface concentration of biotinylated lipids was associated with some increase in hydrocarbon chain disorder and the formation of biotin microdomains. Nonetheless, the size and hydrophilicity of the bound
WO 03/099835 glycopolymer chains led to the generation of a uniform carbohydrate surface coating on a membrane-mimetic thin film.
A glycocalyx-mimetic film was created by the assembly of biotin chain terminated glycopolymers onto a polymeric lipid membrane electrostatically coupled to a polyelectrolyte multilayer. Varying molar compositions (10, 25, and 50 mol %) of acrylate-derivatized biotin-phosphoethanolamine/phosphorylcholine lipid mixtures were prepared as unilamellar vesicles, fused onto the alkyl chains of an amphiphilic terpolymer, and photopolymerized in situ as a planar assembly. Polarized external reflection infrared spectroscopy confirmed the presence of streptavidin. Notably, IR spectroscopy revealed an increase in the conformational and orientational disorder of the lipid hydrocarbon chains with increasing mole fraction of biotinylated lipid. Correlative images obtained by confocal fluorescence microscopy demonstrated that biotinylated lipids cluster at high surface density. Despite the presence of biotin microdomains, the size and hydrophilic characteristics of coupled glycopolymer chains produced a uniform carbohydrate surface coating.
Reagents: All starting materials and synthetic reagents were purchased from commercial suppliers unless otherwise noted. Poly-L-lysine (PLL, approximately 400 kDa) was purchased from Sigma. Alginate (ALG; low viscosity, ca. 60% mannuronic acid) was obtained from Pronova Biomedical (Norway) and used as received. Streptavidin and fluorescein isothiocyanate (FITC) labeled streptavidin were purchased from Calbiochem (San Diego, CA). FITC-labeled lectin (from Psophocarpus tetragonolobus) with binding specific to the galactose residues of the glycopolymer was purchased from Sigma. The synthesis and characterization of a terpolymer (TER) composed of 2-hydroxyethyl acrylate (HEA), sodium styrene sulfonate (SSS), and 7V,7V-dioctadecylcarbamoylpropionic acid (DOD), poly(HEASSS-DOD) 6:3:1, l-palmitoyl-2-(12-(acryloyloxy)dodecanoyl)-SH-glycero-3phosphorylcholine (mono-acrylPC), and l-palmitoyl-2-(12-(acryloyloxy)dodecanoyl)sn-glycero-3-phosphorylcholine (mono-acrylPC), and 1 palmitoyl-2-(12acryloyloxy)dodecanoyl)-sn-glycero-3-phosphoethanolamine (mono-acrylPE) and its biotin derivative (mono-acrylPE-biotin) have been described in detail elsewhere. (Liu, H. et al., Langmuir 2002,18, 1332-1339; Marra, K.G. et al., Macromolecules 1997, 30, 6483-6488; Chon, J.H. et al., J. Biomater. Sci., Polym. Ed. 1999,10, 9523
WO 03/099835
108; Sells, T.D. and O’Brien, D.F., Macromolecules 1994, 27, 226-233; Sun, X.-L. et al., Bioconjugate Chem. 2001,12, 6Ί3-6ΊΊ.)
The biotin chain-terminated glycopolymer was generated by cyanoxylmediated free radical polymerization, as in Example 1. Briefly, 4-aminobenzylbiotinamide was used as the initiator for the polymerization of 2-acrylaminoethyl lactoside with acrylamide. Treatment of the initiator with HBF4 and NaNO2 in deoxygened H2O-THF (1:1) generated an arenediazonium cation, which upon reaction with NaOCN at 50 °C afforded a biotinyl-aryl free radical and a cyanoxyl free radical (.OCtN) as the initiating system. A biotin chain-terminated glycopolymer was generated in 75% conversion as a white spongy powder. The molar mass (Mn) of the polymer was 12 kDa with a polydispersity index (Mw/Mn) of 1.3 determined from size-exclusion chromatography coupled with both refractive index and laser-light scattering detectors. ׳The mole fraction of the lactose-bearing repeat units in the biotinylated glycopolymer was 1:7 lactose/acrylamide with a total of 10 repeat units.
Instrumentation: Contact angles were obtained using a Rame-Hart goniometer, model 100-00. Measurements are reported as the average value plus or minus standard deviation of advancing or receding contact angles of at least 15 data points (5 measurements each per 3 samples).
Infrared Spectroscopy. Spectra were acquired using a Digilab/BioRad FTS4000 Fourier transform infrared (FT-IR) spectrometer (Randolf, MA) equipped with a wide-band MCT detector, collected with 512 background scans, triangular apodization, and 4 cm’<sup>1</sup> resolution. Polarized infrared external reflection spectra were acquired using a Thermo Spectra-Tech 510 external reflection accessory (60° angle of incidence; Shelton, CT) with infrared (IR) radiation polarized perpendicular or parallel to the surface normal using a Thermo Spectra-Tech ZnSe wire grid polarizer. Perpendicular (Rs) and parallel (Rp) polarized external reflection spectra were acquired using the spectrum of a clean silicon wafer as a background. Samples were acquired with 300-450 sample scans depending on the amount of water vapor present in the sample spectrum. Reference spectra of biotin-acrylate-PE and acrylate-PC bulk powders were obtained with a Specac Silvergate (Smyrna,GA) single bounce attenuated total reflection anvil press accessory. Conditions were similar to those
WO 03/099835 PCT/US03/15901 described above, with the exception that the spectra were obtained in an unpolarized format and with 100 background and sample scans. Spectral manipulations performed on the data, such as baseline correction, CO<sub>2</sub> peak removal (from 2250 to 2405 cm'<sup>1</sup>), and center-of-gravity frequency position determination of IR absorption bands, were performed using the Grams/32 software package (Thermo Galactic Industries, Salem, NH). Infrared band assignments were obtained from reference ־ values previously reported in the literature. (Jackson, M. et al., Q. Rev. Biophys. ן
1997,30, 365-429; Goormaghtigh, E.; Cabiaux, V.; Ruysschaert, J.-M. In Subcellular
Biochemistry, Volume 23: Physicochemical Methods in the Study of Biomembranes', Ralston, H.J.H. a. G.B., Ed.; Plenum Press: New York, 1994; pp 329-362; Shriner, R.L., Fuson, R.C., Curtin, D.Y., and Morrill, T.C. The Systematic Identification of Organic Compounds', John Wiley & Sons: New York, 1980.)
Confocal Fluorescence Microscopy. Fluorescence images were acquired using a ZeissLSM510 epifluorescence microscope under 63x (oil) magnification mid illuminated using an argon ion laser at 485 nm. Lower magnification images acquired in air look similar, albeit with less detail compared to those obtained using oil immersion. The oil was added to the film surface immediately prior to the initiation of imaging. Images were acquired using eight co-added scans in line mode for films coated onto silicon substrates. No post-image processing was performed. |
Preparation of Silicon Substrates: Prime grade silicon wafers were purchased from Si-Tech Inc. (Topsfield, MA), were 4 in. in diameter, type P/b (100), with a 4-8 β cm resistivity and 500-550 μχη thickness, and were polished on one side. Slides were cut using a diamond-tipped glass cutter in dimensions of approximately 1.0 in. x ן
I
1.5 in. for infrared external reflection spectroscopy and 0.5 in. x 0.5 in. for confocal fluorescence microscopy. After cutting, the slides were cleaned by sonication in a 1:8 mixture of Multi-Terge detergent:DI water for 15 min followed by rinsing the samples 10 times in deionized water. The sonication and rinsing procedure was then repeated twice using deionized water alone.
Fabrication of Biotin-Functionalized Supported Lipid Membranes:
Preparation of a (PLL-ALG)5-PLL Terpolymer Film on Silicon. PLL and ALG were prepared at concentrations of 0.10 and 0.15 w/v % in phosphate-buffered ,
WO 03/099835 saline (PBS; 20 mM NaH<sub>2</sub>PO<sub>4</sub>, 0.9 w/v % NaCI, pH 7.4), respectively. PLL and ALG alternating monolayers were deposited on silicon using 60s contact times for each solution, followed by three rinses with deionized water (~10 s/rinse) between each coating solution. The (PLL-ALG)5-PLL-coated silicon substrates were then exposed to a 0.1 mM solution of poly(HEA-DOD-SSS) 6:3:1 dissolved in a mixture of 20 mM NaH<sub>2</sub>PO<sub>4</sub>/DMSO (99:1 v/v), pH) 7.41, for 90 s. The (PLL-ALG)5-PLL terpolymer coated samples were then rinsed 7-10 times with deionized water.
Vesicle Fusion. Large unilamellar vesicles (LLTVs) totaling 12 mM lipid (in either 0,10, 25, or 50 mol % biotin-mono-acrylPE/mono-acrylPC mixtures) in 20mM sodium phosphate buffer (pH 7.4) were prepared by three successive freeze/thaw/vortex cycles using liquid N<sub>2</sub> and a 65 °C water bath. The LUVs were then extruded 21 times each through 2.0 gm and 600nm polycarbonate filters (Millipore), and the solution was diluted to 1.2 mM with 20mM sodium phosphate buffer (pH 7.4) and 750mM NaCI. The (PLL-ALG)5-PLL terpolymer-coated substrates were then incubated with the vesicle solution at 43 °C overnight for 14-16h.
In Situ Photopolymerization of a Supported Lipid Film. Details of the photopolymerization of lipid films on alkylated glass and silicon have been reported elsewhere. (Orban, J.M. et al., Macromolecules 2000, 33, 4205-4212; Liu, H. et al., Langmuir 2002,18:1332-1339.) Briefly, a stock solution of coinitiators was prepared as 10 mM Eosin Y (EY), 225 mM triethanolamine (TEA), and 37 mM VP in water. A 10:1 (mol/mol) monomer/EY ratio was used for photopolymerization. After lipid fusion, the samples were placed into aN<sub>2</sub>־purged atmosphere at 30% relative humidity and 10 gL of initiator was added per 1 mL of sample solution. The initiator was gently mixed by slowly rotating the vial in a horizontal circular motion without lifting it from the bench surface. The sample was then irradiated with a Dynalume visible light lamp at an intensity of 50 mW/cm<sup>2</sup>. Following photopolymerization, the samples were washed with deionized water 6-8 times and stored for analysis.
Generation of a Glycocalyx-Mimetic Surface on a Supported Lipid Membrane:
Streptavidin Binding onto a Biotin-Functionalized Lipid Membrane. Streptavidin and FITC-labeled streptavidin, for confocal fluorescence microscopy studies, were prepared in PBST (150 mM NaCI, 50 mM NaH<sub>2</sub>PO4, pH 7.34) at a
WO 03/099835 PCT/US03/15901 concentration of 5 μ/mL. Streptavidin-containing solutions were incubated with biotin-functionalized substrates for 15 min with horizontal shaking, followed by rinsing 10 times with deionized water. ‘ (A
Glycopolymer Binding to a Streptavidin-Functionalized Surface. Streptavidincoated lipid membranes were incubated with biotin-terminated glycopolymer (25 gg/mL) in PBST for 1 h at room temperature with horizontal shaking. The membrane was then washed 10 times with deionized water. For confocal fluorescence microscopy studies, the film was incubated with FITC-labeled P. tetragonolobus lectin (100 Mg/mL) in PBST for Ih at room temperature with horizontal shaking and then washed 10 times with deionized water.
p
A chain-end-functionalized glycopolymer was synthesized in which :
multivalent lactose units serve as ligands for lectins and/or antibodies and a single biotin group on the initiating species provides a convenient anchor to avidin or streptavidin. Modulating lactose density and polymer solubility was achieved by using acrylamide as a comonomer. Binding specificity to streptavidin has been previously verified using a SDS-PAGE gel shift assay and confocal fluorescence imaging of the glycopolymer adsorbed onto a streptavidin-patterned surface (see Example 1).
Fabrication of a Glycocalyx-Mimetic Surface using Biotin-Streptavidin Coupling to a Supported Lipid Film:
We have demonstrated in prior reports that membrane-mimetic films that are stable in air and under static and dynamic flow conditions in an aqueous environment can be produced by in situ polymerization of a planar lipid assembly on a variety of alkylated supports. (Liu, H. et al., Langmuir 2002,18,1332-1339.) Significantly, an alkylated terpolymer, electrostatically coupled to a polyelectrolyte multilayer, allows film fabrication on a hydrophilic cushion that facilitates the incorporation of transmembrane proteins. In this investigation, mixed vesicles, comprised of polymerizable lipids with either biotin or phosphatidylcholine headgroups, were fused onto an alkylated terpolymer bound to a poly-L-lysine/alginate multilayer. Streptavidin and subsequent glycopolymer coating of the polymerized lipid film was then performed to produce a glycocalyx mimic.
WO 03/099835
Contact angles were measured at various stages for films containing 10, 25, or 50 mol % biotin-PE/PC lipids (B-PE/PC) (Figure 2). In agreement with prior studies, advancing contact angles for the ALG/PLL multilayer were low (35°) and increased after the addition of the terpolymer (105-109°). Contact angles for films composed solely of lipids containing a phosphatidylcholine headgroup characteristically range between 50 and 60°. (Orban, J. M. et al., Macromolecules 2000, 33, 4205-4212.) The addition of biotinylated lipids, however, produced a small but noticeable increase in film hydrophobicity, with contact angles of 51, 59, and 77° for films containing 10, 25, and 50 mol % of biotin-PE, respectively. Advancing contact angles were unchanged upon addition of streptavidin or glycopolymer to 10 or 25 mol % biotinPE/PC films. A reduction in film hydrophobicity from 77° to 65° was observed after incubation of the 50 mol % biotin-PE/PC sample with streptavidin. Glycopolymer coating, even at high surface binding density, was not associated with further reduction in contact angle.
Structural Characterization of a GlycocalyxMembrane-Mimetic Film Using Polarized Infrared External Reflection Spectroscopy:
The Effect of Increasing Biotin-PE Film Concentration. Polarized external reflection infrared spectra were acquired during each stage of film construction in order to identify functional group characteristics and induced structural changes unique to each film component. Specifically, infrared spectroscopy provides detailed information regarding hydrocarbon chain conformation and order and, by using polarized spectra, molecular orientation. The level of disorder may influence film properties, such as diffusion across a lipid membrane, as well as the orientation and assembly of membrane-associated proteins. Characteristic IR absorption bands of the component structures of the fabricated glycocalyx-mimetic film are summarized in Table 1.
WO 03/099835
Table 1
Infrared Band Assignments for Components Present in a Glycocalyx-Mimetic Thin Film
<td> absorption mode</td><td> frequency (cm'<sup>1</sup>)</td><td> component of film</td>
<td> OH stretch</td><td> 3600-3000</td><td> ALG, GLY</td>
<td> amide A (mostly N-H)</td><td></td><td> PLL, STREP</td>
<td> amide B</td><td></td><td> STREP</td>
<td> CH2 stretch (antisymm)</td><td> 2926-2918</td><td> TER, B-PE, PC</td>
<td> CH<sub>2</sub> stretch (symm)</td><td> 2853-2850</td><td> TER, B-PE, PC</td>
<td> C=O (ester)</td><td> 1735</td><td> TER, B-PE, PC</td>
<td> amide I</td><td> 1650</td><td> PLL, STREP</td>
<td> COO- stretch (antisymm)</td><td> 1602</td><td> ALG</td>
<td> amide H</td><td> 1550</td><td> PLL, STREP</td>
<td> CH<sub>2</sub> bend (scissoring)</td><td> 1456</td><td> TER, B-PE, PC</td>
<td> COO- stretch (symm)</td><td> 1402</td><td> ALG</td>
<td> PO2- stretch (antisymm)</td><td>-1245</td><td> B-PE, PC (stronger)</td>
<td> C—O—C stretch.</td><td>-1217</td><td> TER, B-PE, PC, GLY</td>
<td> (antisymm)</td><td colspan="2"></td>
<td> C—O—O— C stretch</td><td></td><td> TER, B-PE, PC</td>
<td> (antisymm)</td><td colspan="2"></td>
<td> C=O—O— C stretch ~</td><td> 1100</td><td> TER, B-PE, PC</td>
<td> (symm)</td><td colspan="2"></td>
<td> PO2- stretch (symm)</td><td></td><td> B-PE, PC (stronger)</td>
<td> C—O—C stretch (symm)</td><td>-1030</td><td> TER, B-PE, PC, GLY</td>
<td> (CH3)3N<sup>+</sup> bend (antisymm)</td><td> 975</td><td> PC</td>
<td> (CH3)3N<sup>+</sup> bend (symm)</td><td> 925</td><td> PC</td>
<td> P—O stretch (symm)</td><td> 816</td><td> B-PE, PC</td>
Abbreviations: antisymm, antisymmetric; symm, symmetric; PLL, poly-L-lysine; ALG, alginate; TER, poly(HEA<sub>6</sub>-AOD<sub>3</sub>-SSS1) terpolymer; B-PE, biotin-mono-acrylPE; PC, mono-acrylPC; STREP, streptavidin; GLY, glycopolymer.
Varying the surface concentration of biotin-PE yields several changes in Rs and Rp spectra (Figure 6). On increasing biotin-PE content from 10 to 25 mol %, a decrease is observed in the combination of symmetric C=O—O—C and PO2~ stretches at ~1100 cm<sup>1</sup> in the Rs polarized spectrum (Figure 611, A vs B). In addition, increasing biotin-PE composition is associated with a broadening of the antisymmetric PO<sub>2</sub>— headgroup band at 1250 cm’<sup>1</sup> that appears to shift to a lower wavenumber in both Rp and Rs polarized spectra (Figure 61, Π, A-C). Reference ATR-IR spectra of acrylate-PC and biotinacrylate-PE in powder form demonstrate that both compounds possess PO2— antisymmetric (~1245cm-l) and symmetric (1090cm'<sup>1</sup>) stretches, although the intensities of these bands are significantly reduced
WO 03/099835 in biotin-PE. Thus, it is likely that the observed reduction in intensity at 1100 cm<sup>1</sup>־ in the Rs polarized spectra results from a direct change in film composition (i.e., a reduction in acrylate-PC). Likewise, the shift and broadening of the band at -1250 cm'<sup>1</sup> to a lower wavenumber is due to both a reduction of the PO2— antisymmetric stretch and a simultaneous increase of the C—O—C stretch at 1217cm-l.
The most notable difference in the polarized IR spectra on varying biotin concentration occurs in the va and vs CH2 stretching modes from 3000 to 2800 cm<sup>1</sup> of the Rp polarized spectra, which shift from negative to positive with increasing biotinPE concentration (Figure 61, A-C). The observation of positive and negative absorption bands in polarized spectra has been previously reported in theoretical and experimental studies of monomolecular thin films coated onto silicon substrates. We have also observed this behavior in polymeric lipid films deposited onto OTS/Si and onto (PLL/ALG)5-PLL-poly-(HEA6-DOD3-SSSl) terpolymer/Si coated substrates. Using the Fresnel reflection equations for a three-phase system (Dluhy, R.A., J. Phys. Chem. 1986, 90,1373-1379; Mielczarski, J.A. and Yoon, R.H., J. Phys. Chem. 1989, 93, 2034-2038), we correlated, qualitatively and quantitatively, the positive and negative methylene absorption modes with the molecular orientation of the alkyl chains in the OTS, terpolymer, and supported lipid monolayers. (Orban, J.M. et al., Macromolecules 2000, 33, 4205-4212; Liu, H. et al., Langmuir 2002,18,13321339.) From these investigations, we correlated the positive intensity of the Rp polarized va and vs CH<sub>2</sub> stretching modes with a random alkyl chain orientation that is tilted away from the surface normal and negative CH<sub>2</sub> stretching modes with more ordered alkyl chain packing. In this regard, the negative CH<sub>2</sub> absorption bands observed in the 10 mol % B-PE/PC film (Figure 61, A) are indicative of ordered alkyl chains. An ordered alkyl chain orientation is also supported by the frequency positions of the methylene stretching modes, which can be utilized to assess hydrocarbon chain order. The va and vs CH2 positions of 2919 and 2851 cm’<sup>1</sup>, respectively, indicate that the alkyl chains are only slightly disordered and possess a predominance of trans conformers.
Increasing the concentration of biotin-PE induces alkyl chain disorder. Specifically, in films containing 25 mol % of biotin-PE, the intensity of methylene absorption modes shifts from negative to positive, indicating an increase in random
I *
WO 03/099835 PCT/US03/15901 chain orientation (Figure 61, B). In support of this notion, the va CH<sub>2</sub> band also increases from 2919 to 2920cm<sup>1</sup>־. Further, in films containing 50 mol% of biotin-PE (Figure 61, C), methylene bands are positive and the va CH<sub>2</sub> band shifts to 2925 cm <sup>1</sup>, consistent with disordered hydrocarbon chains containing large numbers of gauche conformers. f
Binding of Streptavidin and Glycopolymer to Biotin-Functionalized Surfaces. Polarized IR spectra obtained after streptavidin binding are presented in Figures 7-9, spectra B. The presence of streptavidin is represented by the appearance of amide A ן (-3300 cm-1) and amide B (-3100 cm'<sup>1</sup>) bands. An additional observation is the increase in the negative intensity of the Rp polarized methylene absorption bands for both the 10 and 25 mol <sup>0</sup>/0B-PE/PC films that represent induced alkyl chain orientation. No appreciable changes were noted in IR spectra after glycopolymer binding (Figures 7-9, spectra C). j
ן
Fluorescence Imaging of Streptavidin and Glycopolymer Bound onto
Membrane-Mimetic Films:
Confocal fluorescence images obtained after incubation of biotin-derivatized films with FITC-labeled showed, as expected, that surface fluorescence increases with increasing concentrations of biotin-PE. Of interest, microdomains of FITC-labeled streptavidin appear on films containing 50 mol% biotin-PE and are thought to indicate a clustering of biotin-PE. The inhomogeneity of the observed fluorescence is related to microphase separation of the PC and biotinylated lipids. Increasing alkyl chain disorder along with a small but noticeable increase in film hydrophobicity is I indicative of incomplete vesicle fusion at high biotin-PE surface concentrations.
Fluorescence images after incubation with FITC-labeled lectin show that glycopolymer-modified surfaces demonstrate a much greater degree of homogeneous fluorescence at 25 and 50 mol % biotin-PE labeling when compared to the corresponding streptavidin-decorated surfaces. This can be attributed to the large amplification of lectin binding sites over the film surface due to the presence of several biotin binding sites on each streptavidin molecule, as well as the availability of approximately 10 pendent lactose units per glycopolymer chain. Relatively little
WO 03/099835 nonspecific lectin or streptavidin binding was noted on membranes composed of phosphatidylcholine lipids alone.
Example 3
Glycopolymers of sulfated lactose exhibit anticoagulant activity.
Glycopolymers of varying molecular weight have been synthesized, as described above, bearing varying backbone densities of sulfated lactose pendent groups. These compounds have been fully characterized by NMR and mass spectroscopy and anticoagulant properties defined using an activated partial thromboplastin time (APTT) assay. Results demonstrate that anticoagulant activity is structure dependent׳ and approaches activity levels observed for heparin and heparinrelated compounds. Figure 10 shows results using a glycopolymer designated SL3 (MW 9300, PDI 1.46) which was a copolymer of sulfated lactose monomers (GM) and acrylamide (AM) (molar ratio AM:GM 1:10, lactose content 57 wt%). Compare with Lovenox control).
Example 4
Glycopolymers bearing lactose heptasulfate dissacharides can stimulate cell proliferation and mediate dimerization of growth factor FGF-2 and growth factor receptor FGFR-1. The capacity of selected glycopolymers to potentiate FGF-2 mitogenic activity was measured by [<sup>3</sup>H]thymidine incorporation into BaF3-FRlC-l 1 cells, which express the FGF receptor, FGFR-1, but not cell surface heparan sulfate. Cells were treated with 3 ng/mL of FGF-2 and increasing concentrations of indicated oligosacharides. Test compounds include a series of glycopolymers ranging in molecular weight, pendent group type and density, as well as corresponding monomers, sucrose octasulfate (SOS), heparin (Sigma porcine intestinal MW 12,00020,000), and heparan sulfate (Sigma MW 7,000). Glycopolymers carrying fully sulfated NAcGlc pendent groups, for example, were ineffective in promoting FGF-2 dependent cell proliferation. However, glycopolymers bearing sulfated lactose residues were able to elicit a range of proliferative activity depending upon the structural features of the polymer (Figure 11). The highest level of bioactivity was demonstrated by SL3-mediated proliferative responses to FGF-2 exceeded those observed with heparan sulfate, as well as SOS and free SL3 monomer. Of interest,
WO 03/099835 PCT/US03/15901 the SL3 effect is selective in that it was not capable of initiating a proliferative response to FGF-1.
Example 5
In order to examine the capacity of SL3 to mediate FGF-2 dimerization, 20 ng/inL of '<sup>25</sup>I-FGF-2 was incubated with either heparin or SL3 for lh at room temperature. After disuccinimidyl suberate cross-linking, the samples were resolved by electrophoresis and visualized by autoradiography. SL3 was as effective as heparin in mediating FGF-2 dimerization. Likewise, SL3 mediated FGFR-1 dimerization was investigated by incubating BaF3-FGFR-lC-l 1 cells with <sup>125</sup>Ilabeled FGF-2 in the presence or absence of either heparin or SL3. Cells were treated with disuccinimidyl suberate to cross-link FGF-2 to its receptor. Crosslinked proteins were electrophoresed on an SDS-6% polyacrylamide gel and detected by autoradiography. SL3 was as effective as heparin in mediating FGFR-1 dimerization. Both FGF-2 and FGFR-1 dimerization are essential for an optimized biological response. It is also noteworthy that FGF-2 is characteristically sequestered in the ECM in a dimerized form.
Example 6
Sulfated lactose glycopolymers protect FGF-2 from protein degradation induced by trypsin, acidic conditions, and heat. It has been suggested that once soluble proteins, such as FGF-2, are released into the extra-cellular matrix, their sequestration by heparan sulfate proteoglycans is essential for preservation of bioactivity. In order to assess protection from proteolysis, FGF-2 (1 pg) was incubated with trypsin for 3 h at 37°C in the presence or absence of 25 pg/mL of heparin or decreasing concentration of glycopolymer SL3. Samples were then analyzed by SDS-PAGE and undigested FGF-2 was estimated by densitometry. SL3 was as effective as heparin in protecting FGF-2 from proteolytic degradation. Protection from acidic conditions was determined by incubation of FGF-2 with or without heparin or glycopolymer (25 pg/mL) in varying concentrations of trifluoroacetic acid (0.05 to 5%), corresponding to a pH range of 0 to 3.4 (133). After a two hour incubation at room temperature, samples were diluted 20 fold with RPMI
WO 03/099835
1640 and incubated with heparin deficient cells (BaF3-FGFR-l) expressing the FGF receptor (FGFR-1). <sup>3</sup>H-thymidine incorporation was determined as an indicator of retained FGF-2 activity. Preservation of biological activity upon heat-treatment of
FGF-2 was measured by incubation of FGF-2 at 65 °C for 5 min with or without heparin or glycopolymer (25 pg/mL). Samples were diluted in RPMI1640 and incubated with BaF3-FGFR-l cells and <sup>3</sup>H-thymidine incorporation determined (Figure 12). Both heparin and the heparin-mimetic glycopolymer provided substantial protection of FGF-2 from trypsin, heat, and acidic conditions.
Although this invention has been illustrated with specific molecules, reagents and reaction conditions, it will be appreciated by those of skill in the art that other such molecules, reagents and reaction conditions may be used or generated, and such equivalents are considered to be within the scope of the following claims.
United States Patent 1!9j
Miyasaka et al.
<img file="IL190885A_D0073.tif" />
IIIIIIIHIIIIIIIIIIIIIIIIIIIIIIIIIIIIIIIIIIIIIIIM
USOO5138O26A
[11] Patent Number: 5,138,026
[45] Date of Patent: Aug, 11,1992
<td> [54]</td><td colspan="2"> POLYPEPTIDE THIN FILM</td>
<td> [75]</td><td> Inventors:</td><td> Tsutomu Miyasaka; Mitsunori Ono; Naoyuki Nishikawa, all of Kanagawa, Japan</td>
<td> [73]</td><td> Assignee:</td><td> Fuji Photo Film Co., Ltd., Kanagawa, Japan</td>
<td> [21]</td><td> Appl. No.:</td><td> 480,699</td>
<td> [22]</td><td> Filed:</td><td> Feb. 15,1990</td>
<td> [30]</td><td colspan="2"> Foreign Application Priority Data</td>
Feb. 15, 1989 [JP] Japan .................. 1-35870
Jun. 2, 1989 [JP] Japan ................. 1-140785
[51] Int. CM.......................C08G 69/10
[52] U.S. 0................. 528/328; 428/411.1;
428/474.4; 428/474.7
[58] Field of Search........... 528/328; 428/411.1,
428/474.4, 474.7
[56] References Cited
U.S. PATENT DOCUMENTS
3,119,794 1/1964 deVries et al............ 528/328
4,743,675 5/1988 Watanabe.............. 528/328
4,857,427 8/1989 Itoh et al............... 528/328
Primary Examiner—Harold D. Anderson Attorney, Agent, or Firm—Sughrue, Mion, Zinn, Macpeak & Seas
[57] ABSTRACT
A polypeptide thin film obtained by polymerizing a monomolecular film comprising an amphiphilic compound having a hydrophobic moiety and a hydrophilic moiety having an amino acid ester structure per molecule, the conjugated acid of the elimination group of said ester having a pKa of not higher than 14, or a builtup film of said monomolecular film; and a process for preparing a material on which said polypeptide thin film is carried.
Claims, 7 Drawing Sheets
5,138,026 film having good orderliness are limited to a small number of compounds.
There is disclosed in A. Laschewsky, J, Am. Chem. Soc., Vol. 109, page 788 (1987) that in the amphiphilic compounds having various unsaturated bonds useful for radiation polymerization, the polymeric groups are carried through spacer groups so as to maintain order.
JP-A-57-159506 (the term “JP-A” as used herein means an “unexamined published Japanese patent application”) discloses that the polymer films of the monomolecular films of unsaturated compounds (surfactants) and built-up films thereof, prepared by radiation polymerization are used as hyper-filtration films.
Conventional methods for polymerizing these compounds having unsaturated bonds by radiation have the following problems. First, turbulence in the arrangement structure or the disordered agglomeration or precipitation of molecules is liable to be caused by polymerization. Hence, the specific molecular design, for example, the introduction of spacer groups into molecules must be made to prevent such a problem arising. Second, irradiation with ultraviolet light or gamma rays poses a problem in that additives often coexisting with polymerizable amphiphilic molecules are decomposed or denatured. Third, films prepared by such a polymerization have very poor compatibility with organisms and their applications to the tissues of organisms as permeability-controlling films for medicines are limited.
Methods for forming a disulfide bond by the oxidative polymerization of dithiols are proposed in J. Am. Chem. Soc., Vol. 109, page 4419 (1987) as polymerization methods which do not require radiation. Further, methods for radical polymerizing the above-described compounds having unsaturated bonds in the presence of initiators are also useful.
In these methods, however, the initiators must be used during polymerization. Hence, there must be required a stage for removing the initiators from the filmforming system after the completion of polymerization. In addition, these methods have a problem in that coexisting materials are affected by the initiators, including oxidation-reduction agents.
To improve compatibility with organisms by improving polymerization forms, methods for self-condensation-polymerizing the molecular films of long-chain alkyl derivatives of amino acids are disclosed in Macromol. Chem. Rapid Commun., Vol. 3, page 167 (1982) and Thin Solid Films, Vol. 133, page 39 (1985), and a method for condensation-polymerizing similar derivatives in the presence of carbodiimide as a condensing agent is disclosed in J. Am. Chem. Soc., Vol. 108, page 487 (1986). However, the condensation reaction in the self-condensation polymerization of these methods proceeds very slowly, and the method using a condensing agent has a problem in that the condensing agent and by-products are left behind and the condensation reaction is hard to handle. This is because the efficiency of the condensation reaction must be controlled.
Methods for preparing monomolecular films by using optical active amino acids and ester derivatives thereof are described in J. Am. Chem, Soc., Vol. Ill, page 1115 (1989) and ibid., Vol. Ill, page 1436 (1989). There is suggested that the molecular arrangement films of these optical active materials give excellent orientation and denseness. However, no method is disclosed therein for strengthening the structure thereof by rapidly selfpolymerizing the films of these amino acid derivatives
POLYPEPTIDE THIN FILM
FIELD OF THE INVENTION
This invention relates to a thin film comprising a <sup>S </sup>molecular assembly and a process for preparing a material on which the same is carried. More particularly, this invention relates to a thin film which is composed of a polymer of an optical active amino acid having peptide <sub>]0 </sub>bonds which has excellent in compatibility with organisms, and a process for preparing a material on which the same is carried.
BACKGROUND OF THE INVENTION <sub>]5 </sub>Molecular assemblies, such as a monomolecular film (monolayer) having a molecular arrangement or builtup film (monolayers=multilayer) formed by building up a plurality of the monomolecular films, are widely employed as materials for electronics devices, materials 20 for surface protection, hyper-filtration membrances which utilize gaseous molecules or ion-permselectivity, functional thin films for sensors and permeability-controlling films for material delivery by utilizing the ultrathinness and denseness thereof. 25
The Lamgmuir-Blodgett process (LB process) is generally known as a method for building up a monomolecular film of an amphiphilic molecule formed at the gas liquid interface on a substrate. The range of use of various LB films prepared by this method has been in- <sup>30 </sup>creased in recent years (see, Solid Physics 17 (12) 45 (1982)).
The molecular assemblies comprising an LB film exhibit various functions due to the molecular orientation and ultra-thinness. However, they have disadvan- <sup>35 </sup>tages in that they are physically delicate and the film structure is liable to be broken, or they have many structural defects depending upon the compounds employed and a high density can not be obtained.
In order to solve the problem of providing a film which has a uniform structure with an excellent packing of molecules, the film structure of the molecular assembly is required to be physically strengthened.
One of effective means for physically strengthening <sub>45 </sub>the film structure of the molecular assembly is crosslinking or polymerization.
With regard to the polymerization of molecular assemblies, such as an LB film and liposome, conventional polymerizable compounds employed and their poly- <sub>50 </sub>merization are summarized in H. Bader et al., Advances in Polymer Science, Vol. 64, page 1 (1985) and R. Biischl, et al., Macromol. Chem. Suppl., Vbl. 6, page 245 (1984).
The study of polymerizable amphiphilic compounds had been active in the 1980’s. Widely used methods 55 employ unsaturated compounds such as vinyl, diene and diacetylene compounds. The unsaturated bonds are cleaved by ultraviolet light (UV) or a radiation, such as gamma rays, so as to carry out polymerization. However, these methods have difficulty in keeping the order 60 of molecular arrangement by distortion due to polymerization after the cleavage of the. unsaturated bonds, though fast polymers can be obtained.
The orientation of the film is greatly influenced by the lengths of the alkyl chains and the type of the termi- 65 nal hydrophilic group, as pointed out in A. Laschewsky and H. Ringsdorb, Mactomolecule, Vol. 21, page 1936 (1988). Hence, compounds providing a polymerized
5,138,026 *
so as 10 prepare a thin film of an optically active polypeptide.
SUMMARY OF THE INVENTION
Accordingly, an object of the present invention is to 5 provide a polymerizable thin film having a good molecular arrangement, which is polymerized without using any radiation and any polymerization initiator, and a process for preparing a material on which the same is carried. <sup>10</sup>
Another object of the present invention is to provide a polymerizable thin film which allows polymerization to proceed spontaneously at a high speed and high yield by self-polymerization, and a process for preparing a material on which the same is carried. Ii
Still another object of the present invention is to provide a polymeric thin film has excellent denseness, as well as compatibility with organisms.
The above objects of the present invention have been achieved by providing: 20 a polypeptide thin film obtained by polymerizing a monomolecular film (monolayer) comprising an amphiphilic (amphiphatic) compound (including an amphiphilic long-chain alkyl derivative of an optical active o-amino acid ester having a same stereo-structure) hav- 25 ing a hydrophobic moiety and a hydrophilic moiety having an amino acid ester structure per molecule, the conjugated acid of the elimination group of said ester having a pKa of not higher than 14, preferably from 10 to 13, or a built-up film (multilayer) of said monomolec- 30 ular film; and a process for preparing a material on which said polypeptide thin film is carried, which comprises (A) forming a monomolecular film comprising an amphiphilic compound having a hydrophobic moiety 35 and a hydrophilic moiety having an amino acid ester structure per molecule, the conjugated acid of the elimination group of said ester having a pKa of not higher than 14, at a gas-liquid interface, and either;
(B) polymerizing said monomolecular film at said 40 interface and then transferring the resulting film onto a substrate, or (B') transferring the monomolecular film or a built-up film prepared from the monomolecular film onto a substrate and then carrying out polymerization. 45
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a graph illustrating isothermal characteristics at 20* C of a surface pressure-molecule occupying area (π-Α), wherein A is a curve for the monomolecular 50 film of the monomer of compound 1-1 and B is a curve for monomolecular film after polymerization at room temperature for 2 hours.
FIG. 2 is a graph illustrating the π-Α isothermal characteristics at 20* C., wherein C is a curve for the 55 monomolecular film of the monomer of compound 1-3 and D is a curve for monomolecular film after polymerization at room temperature for 2 hours.
FIG. 3A is a Voltammograph of the built-up film of the monomer of compound 1-1, wherein curve 1 is for 60 the case where there is no film, curve 2 is for a film composed of 8 layers, and curve 3 is for a film composed of 16 layers.
FIG. 3B is a Voltammograph of the polymerized built-up film of compound 1-1, wherein curve 4 is for 65 the case where there is no film (the same as 1), curve 5 is for a film composed of 4 layers, and curve 6 is for a film composed of 8 layers.
FIG. 4 is a chart showing infrared absorption spectrums of compound 1-3.
FIG. 5 is a graph showing the x-A characteristics at 20* C. of compound 11-6, wherein A is a curve before polymerization and B is a curve after polymerization.
FIG. 6(0) is an electron micrograph (200 X magnification) of an LB film (monomolecular film) prepared by using the long-chain alkyl derivative of the optical inactive amino acid ester prepared in Example 4.
FIG. 6(6) is an electron micrograph (200 X magnification) of an LB film (monomolecular film) prepared by using compound II-6 of the present invention.
DETAILED DESCRIPTION OF THE INVENTION
The polymerized monomolecular film or built-up film of the present invention is an ultra-thin film carried on a substrate by various monomolecular film coating methods including the Langmuir-Blodgett process, and is characterized by the main chain of the polymer being composed of polypeptide, i.e., the chains of amide bonds of amino acids. In the polymerized film of the present invention, amphiphilic amino acid derivatives having a reactive ester group, i.e., electrophilic ester group are subjected to condensation polymerization by the following reaction to form the skeleton of amide bond.
II - II (HjN-CH-C-XR<sup>1</sup>),---> .eCH-C-NH-F,
R R wherein n represents an integer of 2 or greater, and R, R<sup>1</sup> and X are illustrated in the definitions of general formula (1) or (II) hereinafter.
Now, methods for forming the polymerized film of the present invention will be illustrated below.
Any of two of a method comprising carrying out polymerization at the gas-liquid interface and a method comprising carrying out polymerization on a substrate can be used to form the polymerized thin film.
To carry out polymerization at the gas-liquid interface, a monomolecular film of an amphiphilic amino acid ester derivative monomer of the following formula (I) or (II) according to the present invention is prepared by spreading said monomer on a subphase in a trough for the production of monomolecular film with an appropriate solvent. Said film is left to stand on the water surface for a period of time required for polymerization, preferably for 30 minutes to 2 hours. Pure water or a salt solution, such as a buffer solution can be used for the subphase. Preferably, the pH thereof is adjusted to a range of 5 to 9 depending on the equilibrium constant of the ester decomposition of the monomer to be used.
The temperature of the subphase is preferably in the range of from room temperature to 60’ C., more preferably from 20* C. to 45* C. When the temperature is high, the reaction can be accelerated.
The surface pressure during the reaction is kept in the range of preferably 5 to 40 dyne/cm, more preferably 10 to 25 dyne/cm. Generally, the surface pressure is controlled to a given value. If desired, the surface pressure may be increased or reduced as the reaction proceeds. After the completion of the reaction, the polymerized film on the water surface is transferred onto a hydrophilic or hydrophobic substrate by means of
5,138,026
Langmuir-Blodgett process (vertical dipping method) or horizontal dipping method. When one layer of said film is transferred onto the substrate, a polymerized monomolecular film is formed thereon. When many layers of said film are transferred onto the substrate one 5 by one, a polymerized built-up film is formed thereon.
The second method is a method wherein a monomolecular film of an amphiphilic amino acid ester derivative monomer of the following formula (I) or (II) is formed on a water surface and transferred onto a sub- 10 Strate in the manner described above and then the resuiting built-up film is left to stand on the substrate to thereby allow polymerization to proceed. When the monomolecular film is to be built up on the substrate in this method prior to the reaction, it is necessary that the 15 subphase is kept under such conditions that the polymerization reaction is inhibited, for example, the subphase is kept at a low pH of not high as 30’ C. The monomer built up on the substrate can be polymerized by treating it under polymerization accelerating condi- 20 tions, for example, by heating it, treating it with alkaline gas (e.g., NH3) or immersing it in an aqueous alkaline solution.
Of these two polymerization methods, the former gas-liquid interfacial polymerization is preferred from 25 the viewpoint of the permission of reaction. However, the method is not always preferred from the viewpoint of reaction efficiency and the degree of polymerization. They can be properly used depending on the stability of the monomers to be used. 30
Amphiphilic amino acid esters which are used in the present inventioncan be represented by the following general formula (I) or (II). Particularly, amphiphilic optical active amino acid esters are represented by the following general formula (II). 35
O (1)
H
HjN—CH—C—XR׳
R 40
In formula (I), R represents an organic group including a long-chain alkyl group (preferably a straight-chain alkyl group having from 12 to 20 carbon atoms, more preferably from 16 to 20 carbon atoms); XR' is an elimi- 45 nation group whose conjugated acid has a pKa of not higher than 14; X represents — O—, —S—, or —N(R<sup>2</sup>)— (wherein R<sup>2</sup>is hydrogen atom, an alkyl group or an aryl group, and R<sup>2</sup> may be combined together with R<sup>1 </sup>to form a ring which may optionally have hetero-atom 50 such as nitrogen or unsaturated bond). Preferably, X is —O—. Examples of R<sup>1</sup> include an ,aryl group (including a substituted aryl group; examples of the aryl group including phenyl and naphthyl; examples of substituent groups including nitro group and halogen), a halo alkyl 55 group (e.g., mOnochloromethyl, dichloromethyl, trichloromethyl), an acylatnino group (e.g., Nmethylacetylamino, N-methylbenzoylamino), —N=CR<sup>3</sup>(R<sup>4</sup>) (wherein R<sup>3</sup> and R<sup>4</sup> are each hydrogen atom, an alkyl group or an aryl group, and the alkyl 60 group and the aryl group may be substituted), an alkenyl group and an alkinyl group. Among these groups, the aryl group(including the substituted aryl group) is preferred.
Preferred straight-chain alkyl groups of R are those 65 having from 16 to 20 carbon atoms. When said alkyl group is bonded to a residue of an amino acid through a bonding group, said bonding group is preferably —NHCO—, -NHCOO-, -NHCONH-, —NHCO—S—, —0—, —S—, COO—, —ΟΡΟ3θ or a combination of these groups with said alkyl group.
Preferred examples of the amino acid ester (monomers) represented by formula (I), which can be used in the present invention include, but are not limited to, the following compounds.
<img file="IL190885A_D0074.tif" />
NH2
1-2
<img file="IL190885A_D0075.tif" />
C18H37-NHCOO-(CH2)2-CH coo
<img file="IL190885A_D0076.tif" />
<img file="IL190885A_D0077.tif" />
C20H41-O-CH2NH2
<img file="IL190885A_D0078.tif" />
NH2
C17H35-COO-CH2-
<img file="IL190885A_D0079.tif" />
<img file="IL190885A_D0080.tif" />
<img file="IL190885A_D0081.tif" />
C|<sub>8</sub>Hj7—C—NCH2—CH2CH2—CH<sub>־</sub>—CH
<img file="IL190885A_D0082.tif" />
5,138,026
<img file="IL190885A_D0083.tif" />
O
II H
C18H37—O-C-N—CH2CH2CH2CH2—CH
-continued
-continued
NH, Cl
C18H37—CH —C.
:—O—CH2CH
Cl
NH2 c3״
C<sub>ib</sub>H37—ch —C—Ο—N—C—CH3
NH, I
1-19
C18H37-CH-C-O—N
NHj
1-20
NH<sub>2</sub>
C18H37—CH—C—o—N=CH
NHj
C18H37-CH-C-O-N'
CH3 l=CH
<img file="IL190885A_D0084.tif" />
OH
1-12
1-13
Ci8H37-CH-C-O-CH2-CH=CH<sub>2</sub>
NHj
1-21
C18H37-CH-C-O—CH2-C=CH
The amino acid esters of formula (I) can be synthesized through the following synthesis route.
O
II H3N-CH-C—OCH3
R
CH1—C—O—C-NH—CH-C—OCH3
I I
CH3 R ch<sub>3</sub> o
I II CH3—C—O-C-NH
CH3
O CH3 oo
II . I ’ H 11 — CH—C—OR<sup>1</sup> <-- CH3—C—O—C—NH—CH—C—OH <sup>1</sup>1
R CH3R
V
II H2N-CH-C-O-R<sup>1</sup>
R
<img file="IL190885A_D0085.tif" />
<img file="IL190885A_D0086.tif" />
NH2 /“ <sup>N</sup>
<img file="IL190885A_D0087.tif" />
The following synthesis example illustrates the synthesis of the compound where R=C!8H37(n)
Compound Γ (compound 1 where R=C1gH37(n)) 1-14 was synthesized according to the method described in T. Folda, L. Gros, H. Ringodorf, Makromol. Chem.
Rapid Commun., Vol. 3, page 167 (1982). M.P. ofcompound Γ; 94’ to 98* C. IR spectrum (Nujol): 1760 cm<sup>1</sup>־<sup></sup>(ester carbonyl), 3200 cm1640 ,<sup>1</sup>־ cm<sup></sup>, 1550 cm<sup>1</sup>־<sup></sup>(ammonium salt).
j.15 35 g (0.093 mol) of compound Γ was dissolved in 200 ml of tetrahydrofuran. 21 g (0.19 mol) of EtjN was added thereto and the mixture was stirred at room ternperature for 10 minutes.
243 g (0.14 mol) of di-tert-butyl carbonate (a product 1-16 of Tokyo Kaseihin) was added thereto and the mixture 60 as such was stirred at room temperature for 10 hours.
After completion of the reaction, tetrahydrofuran was distilled off under reduced pressure. Extraction was carried out by adding 200 ml of ethyl acetate and 200 ml 1-17 of water. This operation was repeated twice. The result65 ־ ing organic layer was washed with a saturated NaCl solution once and dried over Na2SO4. The organic solvent was distilled off under reduced pressure to give a white crystal. The crystal was recrystallized from
5,138,026 ethanol/hexane to obtain 41 g of compound 2' (compound 2_where R=C!8H37(n)).
m.p. 85” to 88° C.
IR 3350 cm־>(NH) (Nujol)
1760 cm<sup></sup> (ester)
1720 cm -<sup>1</sup> (urethane) g (0.024 mol) of compound 2׳ was dissolved in 200 ml of a mixed solution of tetrahydrofuran CH30H=2:l. 10 ml of an aqueous solution of 2 g (0.05 mol) of sodium hydroxide was added dropwise thereto. The mixture was stirred at room temperature for 12 hours and acidified to pH ־about 4 with dilute hydrochloric acid while cooling it in an ice bath. 200 ml of water was added thereto. Extraction with 100 ml of ethyl acetate was conducted three times. The resulting organic layer was washed with water and dried over Na2SO4 The organic solvents were distilled off under reduced pressure to give a crystal. The crystal was recrystallized from ethyl acetate/hexane to obtain 7.2 g of compound 3׳ [compound where R=C״Hij(n)].
m.p. 121’ to 124 C.
IR 3400 cm<sup>1</sup>־ (NH) (Nujol)
2800 to 2600 cm<sup>1</sup>־ (OH of carboxylic acid) 1720 cm<sup>1</sup>־ (carbonyl of carboxylic acid) 1700 cm<sup>1</sup>־ (urethane)
Active esters having a long-chain alkyl group described above can be prepared by using various alcohols and dicyclohexylcarbodiimide as a condensing agent.
The following preparation is provided to illustrate the case where phenol is used as a typical example.
1.8 g (0.0042 mol) of compound 3' and 0.4 g (0.0043 mol) of phenol were dissolved in 100 ml of ethyl acetate. 0.95 g (0.0046 mol) of dicyclohexylcarbodiimide (a product of Tokyo Kaseihin) was added thereto. The mixture as such was stirred at room temperature for 12 hours and cooled with an ice bath. The resulting precipitates were removed by filtration. The mother liquor was concentrated and the residue was purified by means of silica gel column chromatography, eluting with hexane : ethyl acetate =8:1 as an eluent to give 1.7 g of compound 4a (compound 4 where R=C!0H37(n),
<img file="IL190885A_D0088.tif" />
bath to obtain 0.7 g of the desired compound 1-3 as a white crystal.
The compound was decomposed on standing at room temperature. Therefore, the compound was fed to a film <sup>5</sup> preparing stage without purification after the structure was confirmed by IR spectrums (FIG. 4).
In a similar manner to that described above, other compounds were prepared. The compounds were unstable and hence the melting points of their intermedi<sup>10</sup> ates Ab to 4e to were measured.
<td colspan="2"> Com- 15 pound</td><td> Intermediate</td><td> R</td><td> R<sup>1</sup></td><td> M.P. ___</td>
<td></td><td> 1-18</td><td> 4b</td><td> C|jHj7(n)</td><td> Cl 1</td><td> 102 to 103־ C.</td>
<td> 20</td><td> 1-19</td><td> 4c</td><td> ״</td><td> —CHjCH Cl C<sub>3״</sub></td><td> 99 to 101’ C.</td>
<td> 25</td><td> 1-20</td><td> 4d</td><td></td><td> ch<sub>3</sub>—ס-א-<sub></sub>ן! 0 —CH<sub>2</sub>-CH=CHj</td><td> 95 to 100’ C.</td>
<td></td><td> 1-21</td><td> 4¢</td><td> .</td><td> —CH2-C=CH</td><td> 88 to 89* C.</td>
<td> 30</td><td></td><td></td><td> •</td><td> 0 11</td><td> (11)</td>
h<sub>2</sub>n—CH-C—XR<sup>1</sup>
R
3j In formula (II), R represents an organic group including a long-chain alkyl group (preferably a long-chain alkyl group having from 12 to 20 carbon atoms, more preferably from 16 to 20 carbon atoms); XR<sup>1</sup> represents an elimination group whose conjugated acid has a pKa 40 of not higher than 14; and X represents —O—, —S—, or — N(R<sup>2</sup>)— (wherein R<sup>2</sup> is hydrogen atom, and alkyl group or an aryl group and R<sup>2</sup> may be combined together with R<sup>1</sup> to form a ring which may optionally have heteroatom such as nitrogen or unsaturated bond).
Preferably, X is —O—. Examples of R<sup>1</sup> include an aryl group (including a substituted aryl group; examples of the aryl group including phenyl group and naphthyl group; and examples of substituent groups including nitro group and halogen), an alkyl group (including a <sup>50</sup> substituted alkyl group; e.g., methyl, monom.p. 125* to 129’ C. IR 3360 cm<sup></sup> (NH) (Nujol)
1780 cm<sup></sup> (ester)
1695 cm<sup></sup> (urethane)
1600 cm<sup>-</sup>(substituted benzene) g of the compound 4a was dissolved in 10 ml of anhydrous chloroform, and the resulting solution was cooled in an ice bath to 0’ C. 5 ml of CF3CO2H was added thereto and the mixture was stirred at 0’ C. for 30 minutes. The solvent was distilled off under reduced pressure. The resulting white crystal was again dissolved in 20 ml of chloroform, and the chloroform layer was washed with 10 ml of a 5% aqueous solution of 65 NaHCO3 twice. The chloroform layer was then washed with water and dried over Na2SO4. The solvent was distilled off under reduced pressure while using an ice chloromethyl, dichloromethyl, trichloromethyl), an acylamino group (e.g., N-methylacetylamino, Nmethylbenzoylamino), —N=CR<sup>3</sup>(R<sup>4</sup>) (wherein R<sup>3</sup> and R4 are each hydrogen atom, an alkyl group or an aryl <sup>55</sup> group, and the alkyl group and the aryl group may be substituted), an alkenyl group (e.g., allyl) and an alkinyl group (e.g., acetyl). Among these groups, the alkyl group, the alkinyl group and the aryl group are pre<sub>M</sub> ferred.
Preferred long-chain alkyl groups of R include those having from 16 to 20 carbon atoms. When said alkyl group is bonded to a residue of an amino acid through a bonding group, said bonding group is preferably —NHCO , —NHCOO—, NHCONH-, -NHCO—S—, —O—, —S—, —COO—, — OPO®3— or a combination of these groups with an alkyl group or a substituted aryl group.
5,138,026
12
Preferred examples of the optic esters (monomers) represented by but are not limited to, the follow!:
<img file="IL190885A_D0089.tif" />
active amino acid rmula (Π) include, compounds.
11-1 c=O
I
NHC<sub>16</sub>H33
CH3—o-c nh<sub>2</sub> s
Ό
I
C=O
I
NHC16H33
-continued <sup>h</sup>2N c-o-ch<sub>2</sub>-c=ch I (CH<sub>2</sub>)4
NH I
O=C I C<sub>15</sub>H31
11-2
II-3
<img file="IL190885A_D0090.tif" />
HC=C—CH<sub>2</sub>—O-C NHj
S 0 I C=O I NHC16H33
<img file="IL190885A_D0091.tif" />
<img file="IL190885A_D0092.tif" />
C16H33
I c=o I NHC16H33
<img file="IL190885A_D0093.tif" />
O
<img file="IL190885A_D0094.tif" />
11-5
H<sub>2</sub>
<img file="IL190885A_D0095.tif" />
R C<sub>I6</sub>H33
C-O-CH3
<img file="IL190885A_D0096.tif" />
O
<td> h<sub>2</sub>n</td><td> C-O-CH3</td>
<td> ר <sup>50</sup> 11.6</td><td> 1</td>
<img file="IL190885A_D0097.tif" />
C14H33
<img file="IL190885A_D0098.tif" />
<img file="IL190885A_D0099.tif" />
C16H33
5,138,026
Π-18
<img file="IL190885A_D0100.tif" />
<img file="IL190885A_D0101.tif" />
C18H37
<img file="IL190885A_D0102.tif" />
<img file="IL190885A_D0103.tif" />
Π-19
Methods for synthesizing the optical active amino 40 acid esters of formula (Π) according to the present invention are roughly classified into the following two.
One of them is a method wherein optical active amino acids are used as starting materials and they are converted into the desired compounds while retaining chi45 rality. The other is a method wherein the synthesis of racemes are allowed to proceed and optical active compounds are obtained by using resolving reagents such as brucine.
Typical examples of the methods include, but are not 50 limited to, the following synthesis methods.
<img file="IL190885A_D0104.tif" />
5,138,026
<img file="IL190885A_D0105.tif" />
Step 1
A solution of 200 mg (110 mmol) of p-toluenesulfonic acid (PTS) in 2 ml of tetrahydrofuran (THF) was added dropwise to a mixed solution of 21 g (96 mmol) of Boc-1serine methyl ester 1,40 g (480 mmol) of 2,3-dihydropyran (DHP) and 450 ml of CHC13. The mixture was stirred for 3 hours. After DHP and CHC13 were distilled off under reduced pressure, 200 ml of CHCI3 was added to the residue. Washing with an aqueous 5% NaHCO3 solution, water washing and drying over Na<sub>2</sub>SO4 were carried out, and CHCI3 was distilled off under reduced pressure. The thus-obtained solid was dissolved in 500 ml of MeOH. A solution of 4.5 g (100 mmol) of 93% NaOH in 80 ml of H<sub>2</sub>O was added thereto and the mixture was left to stand overnight. After the solvents were distilled off, water was added to the residue. The water layer was washed with AcOEt, and 200 ml of AcOEt was added thereto. The water layer was acidified (pH=about 3) with dilute HC1. Extraction with AcOEt, water washing and drying over Na<sub>2</sub>SO4 were carried out. AcOEt was distilled off under reduced pressure to obtain 21 g (73 mmol) of carboxylic acid 2 as a high-viscosity liquid.
Step 2
A mixed solution of 2.80 g (9.7 mmol) of carboxylic acid 2, 1.57 g (9.7 mmol) of carbonyldiimidazole and 70 ml of THF was stirred for one hour. A solution of 0.91 g (9.7 mmol) of phenol in 30 ml of THF was added thereto. The mixture was stirred at room temperature for one hour, then under reflux for 1.5 hours and left to stand overnight. The solvent was distilled off under reduced pressure. 200 ml of AcOEt was added to the residue. Water washing was conducted three times, and then drying over Na2SO4and distillation under reduced pressure were carried out. The residue was purified by means of silica gel column chromatography (eluting with hexane/AcOEt=9/l) to obtain 1.37 g (3.8 mmol) of the phenyl ester 3 as a colorless solid. Yield: 39%.
The structure of compound 3 was confirmed by IR, <sup>1</sup>H-NMR and MASS.
IR (KBr}3300 cm1780 ,<sup>1</sup>־ cm1700 ,<sup>1</sup>־ cm1230 ,<sup>1</sup>־ cm<sup>1</sup>־
Step 3
950 mg (5 mmol) of PTS was added to a mixed solution of 5.5 g (15 mmol) of phenyl ester 3, 200 ml of MeOH and 20 ml of H<sub>2</sub>O. The mixture was stirred for 2 hours at room temperature.
950 mg (5 mmol) of PTS was then added thereto and the mixture was stirred for 2 hours. The solvents were distilled off under reduced pressure. The residue was purified by means of silica gel column chromatography, eluting with hexane/AcOEt = 7/3 to obtain 1.2 g (4.2 mmol) of compound 4 (Yield : 28%).
The structure of compound 4 was confirmed by IR, <sup>1</sup>H-NMR and MASS.
Compound 4 was decomposed when a CHC13 solution of compound 4 was washed with an aqueous NaHCO3 solution.
IR (KBr) 3500 cm3240 ,<sup>1</sup>־ cm1780 ,<sup>1</sup>־ cm1700 ,<sup>1</sup>־ cm<sup>1</sup>־
Step 4
1.2 g (6.0 mmol) of trichloromethyl chloroformate (TCF) was added dropwise to 300 mg of activated carbon. Then, phosgene gas generated, was blown into 50 ml of CH2C12 while cooling them with ice. A mixture of 1.18 g (4.2 mmol) of Boc-l-serine phenyl ester 4,0.42 g (4.2 mmol) of Et3N and 25 ml of CH<sub>2</sub>C12 was dropwise added thereto for a period of 30 minutes while cooling them with ice. After the mixture was stirred for 3 hours, N2 was blown into the mixture to expel phosgene. A mixture solution of 1.14 g (4.2 mmol) of stearylamine, 0.42 g (4.2 mmol) of Et3N and 50 ml of CH<sub>2</sub>C1<sub>2 </sub>was added thereto. After the mixture was left to stand overnight, the organic layer was washed with water and dried over Na<sub>2</sub>SO4. Evaporation under reduced pressure was carried out, and the residue was chromatographed on a column of silica gel, eluting with hexane/AcOEt = 8/2 to obtain 1.18 g of a fraction containing compound 5. A portion of this (400 mg) was recrys5,138,026
2. E. M. Landan, S. Grayer Wolf, L. Leiserowitz, M.
Lahaw. J. Sagiv. J. Am. Chem. Soc., Vol. Ill, page
1436 (1989) tallized from AcOEt to give 0.32 g (0.56 mmol) of compound 5.
The structure of compound 5 was confirmed by IR,
Synthesis route Cl
Optical active a-aminoslearic acid
<img file="IL190885A_D0106.tif" />
o—ch<sub>3</sub>
C16H37
<img file="IL190885A_D0107.tif" />
C|6H}7
<img file="IL190885A_D0108.tif" />
step 1
<img file="IL190885A_D0109.tif" />
<sup>1</sup>H-NMR and MASS.
Compound 5 was partially decomposed on the silica gel chromatograph
IR (KBr) 3250 cm<sup>1780</sup><sup>1</sup>־ cm1750 ,<sup>1</sup>־ cm1695 ,<sup>1</sup>־ cm<sup>1</sup>־
Step 5
200 mg (0.35 mmol) of compound 5 was dissolved in a mixed solution of 4 ml of trifluoroacetic acid (TFA) * . and 4 ml of CH2C12- The mixture was stirred for 30 minutes. The solvents was distilled off under reduced pressure. Further, CH2C12 was added and evaporated under reduced pressure. This operation was repeated twice. The residue was dried in vacuo to obtain quanti* tatively compound II-1. 100 mg (0.17 mmol) thereof was dissolved in CHC13 and treated with a cold aqueous solution of NaHCOa The organic layer was dried over Na2SO4 and distillation under reduced pressure was carried out. There was obtained 60 mg (0.13 mmol) of the desired lipid II-l.
The structure of compound 11-1 was confirmed by IR, <sup>1</sup>H-NMR and MASS.
[α]ο24=+6.0 (C= 1.0, CHCh)
IR (KBr) 3500 cm1765 ,<sup>1</sup>־ cm1695 ,<sup>1</sup>־ cm<sup>1</sup>־
Synthesis of compounds II-9 and II-l 1
Methods of optically resolving a-amino-stearic acids as starting materials with brucine are described in the following two literature and were carried out by refer- ״ ring thereto.
1. A. K. Mills, A. E. Wilder Smith, Helv. Chim. Acta, Vol. 43, page 1915 (1960)
Step 1
49.4 g (0.14 mol) of compound 1 was dissolved in 300 ml of methanol. 14.1 g (0.14 mol) of triethylamine was added thereto and the mixture was stirred at room ternperature.
24.3 g (0.14 mol) of di tert-butyl carbonate (a product of Tokyo Kaseihin) was added thereto and the mixture as such was stirred at room temperature for 10 hours.
After the completion of the reaction, methanol was distilled off under reduced pressure. Extraction was carried out by adding 200 ml of ethyl acetate and 200 ml of water. This operation was repeated twice. The resulting organic layer was washed with saturated NaCI solution once and dried over Na2SO4.
The organic solvent was distilled off under reduced pressure to give a white crystal. The crystal was recrystallized from ethanol/hexane to give 41 g of the desired compound 2.
m. p. 85 to 88 C.
IR 3350 cm<sup>1</sup>־ (NH) (Nujob)
1760 cm<sup>1</sup>־ (ester)
1720 cm<sup></sup> (urethane) step 2 mol) of compound 2 was dissolved in 200 ml of a mixed solution of tetrahydrofuran : CH3OH=2:1, and 10 ml of an aqueous solution of 2 g (0.05 mol) of sodium hydroxide was added dropwise thereto.
The mixture was stirred at room temperature for 12 hours and then acidified to pH=about 4 with dilute hydrochloric acid while cooling it with an ice bath. 200
5,138,026 ml of water was added thereto. Extraction with 100 ml of ethyl acetate was carried out three times. The organic layer was washed with water and dried over
Na<sub>2</sub>SO4.
The organic solvent was distilled off under reduced 5 pressure to give a crystal. The crystal was recrystallized from ethyl acetate/hexane to obtain 7.2 g of the desired compound 3. m. p. 121 to 124' C.
IR 3400 cm<sup>1</sup>־ (NH) (Nujol) <sup>10</sup>
2800 to 2600 cm<sup>1</sup>־ (OH of carboxylic acid) 1720 cm<sup>1</sup>־ (carbonyl Of carboxylic acid) 1700 cm<sup></sup> (urethane) step 3 15 g (0.05 mol) of compound 3 and 4.7 g (0.05 mol) of phenol were dissolved in ethyl acetate, and the mixture was stirred at 0' C.
10.3 g (0.05 mol) of DCC (dicyclohexylcarbodiimide) was added thereto, and the mixture was stirred at room <sup>2 </sup>temperature for 10 hours. The precipitate was removed by filtration, and the residue was purified by means of silica gel column chromatography (eluent hexane: ethyl acetate=4:l) to obtain 23 g of the desired compound 4 as a colorless oil
<img file="IL190885A_D0110.tif" />
IR (neat) 3450 cm1780 ,<sup>1</sup>־ cm1700 ,<sup>1</sup>־ cmStep 4 <sub>35</sub> g (0.02 mol) of compound 4 was dissolved in 100 ml of CH2C12, and the mixture was cooled to —10' C. 20 ml of trifiuoroacetic acid was added thereto, and the mixture was stirred at 0* C. for 30 minutes.
After volatile matters were distilled off under re- 40 duced pressure, the residue was dissolved in ethyl acetate. The organic layer was washed with a 5% aqueous solution of NaHCO3 three times and dried over Na<sub>2</sub>SO4 The solvent was distilled off under reduced pressure to give the desired compounds 11-9 and 11-11. *5
The compound was unstable. Hence, the compound was fed to a film-preparing stage without purification.
ll-9[a]p“+14' (C=0.5CHCb) (TFA salt) : IR = 3400 cm1765 ,<sup>1</sup>־ cm<sup>1</sup>־
11-11: <sup>50</sup>
[o]d« +12’ (C=0.5CHCb) (TFA salt) : IR3350־cm1760 ,<sup>1</sup>־ cm<sup>1</sup>־ (KBr)
Other compounds represented by formula (II) can be prepared in a similar manner to that described above.
Various organic or inorganic materials having a hy- <sup>55 </sup>drophilic or hydrophobic surface can be used as substrates (supports) to be coated with the monomolecular film or built-up film in the present invention. These materials may be flat, or may have porous or fibrous three-dimensional network structure.
Examples of the flat materials include electrically conductive materials such as metals, vitreous inorganic materials (e.g., glass, quarts), other inorganic insulating materials (e.g., alumina), various inorganic and organic crystals, inorganic semiconductors (SnO2, In<sub>2</sub>O3, ZnO, TiO2, WO3, GaAs, Si), organic semiconductors, organic electrical conductors, organic polymers and composite materials thereof. The materials may be electrodes connected with external electric circuits or other components such as sensors (e.g., field effect transistor).
Porous or fibrous materials are useful as substrates when mainly used as permeable films or filters. Exampies of the porous or fibrous materials include organic and inorganic microporous filters, cellulose resin films and various porous polymer films.
Examples of solvents for spreading the monomolecular film, which are used in the present invention include conventional volatile nonpolar solvents, such as chloroform, dichloromethane, benzene, toluene and ether and mixtures thereof with hydrophilic polar solvents, such as alcohols and water.
Various building-up methods including the LB process can be used for coating the surface of the substrate or the support with the monomolecular film on a water surface. The LB process which is a vertical dipping method is described in J. Am. Chem. Soc., Vol. 57, page 1007 (1935); G. L. Gains, Jr., Insoluble Monolayers at Liquid-Gas Interfaces, (Interscience), N.Y. written by Kiyonari Fukuda (1986).
In addition thereto, other methods such as horizontal dipping method and rotating dipping method (e.g., described in JP-A-60-189929, JP-A-61-42394) can be used as coating methods. The built-up film can be obtained by carrying out repeatedly an operation of coating the substrate with the monomolecular film.
Improved horizontal dipping method described in Japanese Patent Application No. 63-54680 (correspond30 ing to JP-A-1-228539) or continuous building-up method described in JP-A-60-209245 may be used for effectively carrying out building-up.
The present invention is now illustrated in greater detail by reference to the following examples which, however, are not to be construed as limiting the invention in any way.
EXAMPLE 1
Compound 1-1 was used as the amphiphilic amino acid phenyl ester and dissolved in dichloromethane to a concentration of 1 mM, thus preparing a spreading solution. The solution was spread on the subphase of 10-<sup>3</sup>M phosphate buffer solution (pH 7.4) by using Langmuir’s film balance to prepare a monomolecular film. Immediately after the preparation, the monomolecular film was compressed at a rate of 10 cm<sup>2/</sup>min by means of belt drive barrier, and the surface pressuremolecule occupying area (ff-A) characteristics at 20 C. of the monomolecular film were measured. There was obtained the result (curve A) of FIG. 1. It was seen from the π-Α characteristics that a good monomolecular film was formed. The monomolecular film was left to stand on the subphase of the buffer solution under a given surface pressure of 15 dyne/cm at room temperature for about 2 hours to thereby allow polymerization to proceed. After standing, the tr-A characteristics were again measured. There was obtained the result (curve B) of FIG. i. It is clear from curves A and B that the molecule is densified by polymerization, the film is shrunk, the breaking strength is improved and hence the film is strengthened.
The polymerized film was compressed to 30 dyne/cm, and 40 layers thereof were built up on a golddeposited glass substrate by means of horizontal dipping method. Fourier transduction infrared absorption spectrums of the built-up film were measured on the gold surface by reflection absorption method. It was found that absorption bands specific to the phenyl ester disap5,138,026 peared, absorption bands showing the formation of amide bonds appeared at 1650 to 1700 cm<sup></sup> and hence a polypeptide was formed by polymerization. Further, the spectrums of a sample built up on a silicon substrate were measured by the permeation method and compared with the above spectrums. It was found that in the reflection method, absorption in C-H expansion of the long-chain alkyl group was remarkably lowered in comparison with absorption in C=O expansion of the amide. Hence, the axis of long-chain alkyl group was !0
Absorption spectrums were measured. Weak broad absorption at 1600 to 1700 cm<sup>1</sup>־ due to apparently the formation of amide bonds was observed. However, sharp absorption of the ester group was still left and the <sup>5</sup> reaction was not completed. It was considered that the polymerization rate of the alkyl ester derivative was lower by a number of at least two figures than that of the aryl ester derivative of the present invention.
EXAMPLE 3 orientated in the direction perpendicular to the plane of the substrate. Accordingly, it could be confirmed that molecular arrangement was maintained.
EXAMPLE 2 <sub>״</sub>
Compound 1-3 was used as the amino acid phenyl ester and a spreading solution was prepared in the same way as in Example 1. The π-Α characteristics at 20’ C. were measured, and curve C of FIG. 2 was obtained for the monomer before polymerization. The monomolecu- 20 lar film was left to stand on a water surface having a pH of 7.4 at 35’ C. under a constant surface pressure of 25 dyne/cm for about 80 minutes to thereby allow polymerization to proceed. After the polymerization, the π-Α characteristics were again measured, and curve D <sub>2</sub>5 of FIG. 2 was obtained. It is clear from curves C and D that the film is shrunk and strengthened.
After the lapse of various times from 1 to 60 minutes, about 40 layers of the monomolecular film were built up οϋ a Si wafer substrate by the horizontal dipping <sub>30 </sub>method to measure polymerization rate. The infrared absorption spectrums of the built-up film were measured by the permeation method, and the rate of decrease in the characteristic absorption (-1750 cm־') of the phenyl ester was examined. It was found that about 50% of the ester disappeared after the reaction for 10 minutes, about 90% of the ester disappeared after the reaction for 60 minutes and amide bonds were formed.
COMPARATIVE EXAMPLE
For the purpose of comparison, the following amphiphilic amino acid methyl ester monomer was used. In the same way as in Example 1, a monomolecular film was formed on the water surface and polymerized.
nh<sub>2 </sub>C18H37—CH—COOCHj
An aqueous buffer solution having a pH of 7.4 was used as subphase, and measurements were made at two points of 20’ C. and 35’ C. The π-Α characteristics at 20’ C. of the above monomer were similar to those of compound 1-3, and the breaking pressure was about 35 dyne/cm. The monomolecular film was left to stand on the subphase at 20’ C. and 35’ C. under constant surface pressure of 15 dyne/cm for about 2 hours. However, change in the area of the film was scarcely caused.
In the same way as in Example 2,40 layers of the film were built up on the Si wafer substrate. FT-IR spectrums were measured. In both cases of temperatures, the 60 built-up film exhibited IR spectrums wherein the strong absorption (~ 1730 cm־') of the ester remained, and the amide bond was scarcely formed. Further, the monomolecular film was left to stand on a subphase having a pH of 9 under a surface pressure of 15 dyne/cm for 65 about 20 hours, said pH value elevating the activity of the ester. Thereafter, the monomolecular film was built up in the same way as in the above-described operation.
In the same way as in Example 1,4 to 16 layers of the polymerized film of the compound used in Example 1 were built up on the surface of a glassy carbon electrode under 30 dyne/cm. The permeability was evaluated on the basis of electrochemical measurement.
Metal ion as an object to be permeated was chosen as substrate. The polymerized film-coated glassy carbon electrode was immersed in a neutral electrolytic solution consisting of 1 mM K3Fe(CN)6and 10 mM KN03. The rate of Fe<sup>3</sup>+ ion to be passed through the polymerized film was measured by means of cyclic voltammetry of oxidation-reduction current of Fe<sup>3+</sup>/Fe<sup>2+</sup>. The electrade potential was controlled against a saturated calomel electrode. Electrolysis was carried out under N2gas purge. The voltammogram was measured after potential was repeatedly scanned about 30 times. Voltammetry was carried out for the. polymerized film of the present invention as well as the film built up on the electrode immediately after spreading the monomolecular film of the monomer before polymerization. Both were compared with each other.
The results are shown in FIG. 3A and 3B.
In the built-up film of the monomer (FIG. 3A), the peak of current value (corresponding to the amount of Fe<sup>3</sup>+ passed through the film), shown by the cyclic voltammogram, was beginning to cause markedly lowering in the peak value when the number of layers was about 8 (curve 2). When 16 layers were built up (curve
3), the value was lowered to about 1/7 of the peak. In the polymerized film, i.e., polypeptide film (FIG. 3B), the current value was lowered to about 1/5 by the building-up of 4 layers (curve 5) and reduced by about two orders by 8 layers (curve 6).
Thus, it is clear that a remarkable permeation-inhibiting effect can be obtained by polymerization. The voltammogram of the methyl ester of the Comparative Example was measured. The current value was lowered to only i to J by the building up of 8 layers. Therefore, <sup>0</sup> the current-inhibiting effect was low.
EXAMPLE 4
Compound II-6 was used as the amphiphilic amino <sub>J5</sub> acid phenyl ester. In the same way as in Example 1, a spreading solution was prepared, and the π-Α characteristics at 20’ C. were measured. The result (curve A) of FIG. 5 was obtained for the monomer before polymerization.
The monomolecular film was left to stand on an aqueous buffer solution (pH 7.4) under a constant surface pressure of 15 dyne/cm for about one hour to thereby allow the monomer to be polymerized. After the polymerization, the π-Α characteristics were again measured. The result (curve B) of FIG. 5 was obtained. It is clear from curves A and B that the area of the film is shrunk to i by polymerization, the molecule is densified and the breaking pressure is improved.
5.138.026
The monomolecular film after polymerization was built up on a silicon wafer substrate by the LB process, and FT-IR absorption spectrums of the built-up film were measured by the permeation method. It was found that the characteristic absorption ( — 1750 cm<sup>1</sup>־־) of the 5 ester was lowered and the absorption (—1650 cmי ־־) of amide bonds originating from the polypeptide appeared. Therefore, it could be confirmed that polymerization took place. It was estimated on the basis of the absorption intensity that reactivity after polymerization 10 for about one hour was 80 to 90%.
To evaluate the orientation of the molecule after polymerization, the orientation of functional group was examined by comparing FT-IR absorption spectrums of the permeation method with those of the refection ab- 15 sorption measurement. It was confirmed that the polymerization molecule was orientated in such a manner that the axis of the long-chain alkyl group was orientated in the direction perpendicular to the plane of the film. Further, the film thickness of the built-up film 20 formed on the silicon wafer substrate was measured by means of ellipsometry. The film thickness was 20±5 A per one layer and it was suggested that the film was arranged with a thickness of nearly molecular length.
One layer of polymerized monomolecular film coated 25 on the silicon wafer was observed by SEM to examine the morphology of the polymerized film. For the purpose of comparison, the following long-chain alkyl derivative of the optical inactive amino acid ester (a mixture of d-isomer and 1-isomer) was polymerized on 30 the water surface under the same conditions as those for compound 11-6 so as to prepare a polymerized film which was then observed by SEM.
<img file="IL190885A_D0111.tif" />
It was observed that the polymerized film [FIG. 6 (א)] prepared from the optical active amino acid ester of the present invention had a structure denser than that of the polymerized film [FIG. 6 (a)] prepared from the optical 45 inactive amino acid ester.
The relative degree of polymerization of these polypeptide films was examined by using a fluorescent labeling method in combination with a ninhydrin reaction for the determination according to end-group analysis 50 for the determination of primary amino group. The optical active polypeptide film of the present invention had a degree of polymerization which was at least 1.5 times that of the optical inactive polypeptide film.
While the invention has been described in detail and 55 with reference to specific embodiments thereof, it will be apparent to one skilled in the art that various changes and modifications can be made therein without departing from the spirit and scope of the present invention.
What is claimed is: 60
1. A polypeptide thin film obtained by spontaneous polymerization of a film comprising an amphiphilic amino acid derivative monomer represent by formula (I):
o (1)
HjN—CH—C—XR<sup>1</sup>
R wherein R represents an organic group; XR<sup>1</sup> is an elimination group whose conjugated acid has a pKa of not higher than 14; X represents —O—, — S—, or — N(R2)—; R1 represents an aryl group; and R<sup>2</sup> represents a hydrogen atom, an alkyl group or an aryl group, or R<sup>1 </sup>and R<sup>2</sup> are combined together to form a carbocylic or heterocyclic ring.
2. A polypeptide thin film obtained by spontaneous polymerization of a film comprising an optically active amphiphilic amino acid derivative monomer represented by formula (II):
o (11) • H HjN-CH-C-XR'
R wherein R represents an organic group; XR<sup>1</sup> is an elimination group whose conjugated acid has a pKa of not higher than 14; X represents —O—, —S—, or —N(R2)—; R1 represents an aryl group; and R<sup>2</sup> represents a hydrogen atom, an alkyl group or an aryl group, or R<sup>1 </sup>and R<sup>2</sup> are combined together to form a carbocyclic or heterocyclic ring.
3. A polypeptide thin film as claimed in claim 1, wherein R represents a long chain alkyl group.
4. A polypeptide thin film as claimed in claim 3, wherein R represents a straight-chain alkyl group having from 12 to 20 carbon atoms.
5. A polypeptide thin film as claimed in claim 4, wherein R represents a straight-chain alkyl group having from 16 to 20 carbon atoms.
6. A polypeptide thin film as claimed in claim 1, herein R<sup>1</sup> is an aryl group, a halo alkyl group, an alkenyl or an alkinyl group, an acylamino group, or —N=CR<sup>3</sup>(R4), wherein R<sup>3</sup> and R<sup>4</sup> are each hydrogen, an alkyl group, an aryl group, a substituted alkyl group, or a substituted aryl group.
7. A polypeptide thin film as claimed in claim 2, wherein R represents a long chain alkyl group.
8. A polypeptide thin film as claimed in claim 7, wherein R represents a straight-chain alkyl group having from 12 to 20 carbon atoms.
9. A polypeptide thin film as claimed in claim 8, wherein R represents a straight-chain alkyl group having from 16 to 20 carbon atoms.
10. A polypeptide thin film as claimed in claim 2, wherein R<sup>1</sup> is an aryl group, a halo alkyl group, an alkenyl group, an alkinyl group, an acylamino group, or —N=CR<sup>3</sup>(R<sup>4</sup>), an alkenyl, wherein R<sup>3</sup> and R<sup>4</sup> are each hydrogen, an alkyl group, an aryl group, a substituted alkyl group, or a substituted aryl group.
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Polyelectrolyte multilayers based on amphiphilic polysaccharides: Application for entrapment and release of hydrophobic molecules Karine Glinel, Aurdlie Guyomard, Emmanuelle D6, and Guy Muller.UMR 6522, Polymdres, Biopolymdres, Membranes, CNRS-Universito de Rouen, Boulevard Maurice de Broglie, Mont Saint Algnan, F-76821, France
The immobilization of hydrophobic drugs or biomolecules at solid/liquid interfaces is of the promising potential interest for the preparation of bioactive surfaces. Recently we successfully prepared layer-by-layer (LbL) polyelectrolyte assemblies based on polysaccharides hydrophobically modified by alkyl chains. We provided the evidence that these amphiphilic biopolymers are adsorbed in aggregated conformation during the LbL process. This behavior resulting from intra and intermolecular interactions between alkyl chains, suggests the formation of hydrophobic microdomains in the multilayers which are of interest for entrapment of hydrophobic biomolecules. We systematically investigated the loading behavior of a small hydrophobic dye in the LbL films based on these amphiphilic biopolymers. We showed that the loading capacity of these self-assemblies depends on the amount of alkyl chains grafted on the polysaccharide. The loaded dye can be subsequently released by varying the external conditions such as pH and ionic strength. In addition, we will present the first results dealing with the entrapment of an hydrophobic antibacterial polypeptide in these amphiphilic films.
Assembly of Polymers and Nanoparticles -- From. 2-D to 3JD
Division, of Polymeric M ate ria Is:. Science and Eng ineering
The 230th ACS. National Meeting, in Washington. DC, Aug 28-Seot 1, 2005 file://E:\230TH\PMSE\P888364.HTR
03.05.2007
BNSDOCID: <XP_______Β07045ΘΑ—L>
IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
CROSS-REFERENCE TO RELATED APPLICATION
This application claims the benefit of U.S. Provisional Application No. 60/729,828 filed October 25,2005, which is incorporated by reference herein.
BACKGROUND
[0001] Vaccines have been important in medicine ever since it was observed that, for certain diseases, initial exposure to the infectious agent conferred immunity against subsequent infections. Vaccines have been used for many years in order to build immunity in an individual against infection by particular pathogens such as viruses, bacteria, fungi, and parasites. Vaccines have also been used to stimulate the body’s ability to mount an immune response against antigens on cancer cells, or against the formation of pathological fibrils. Vaccines can be administered via various routes including, for example, oral, intravenous, subcutaneous, transdermal, sublingual, intramuscular, and nasal administration.
[0002] Early vaccines relied on “live” or “killed” pathogens that retained their immunogenicity. A better understanding of the structure and function of particular pathogens and of the mechanisms of adaptive immunity has made it possible to design safer and more directed vaccines. For example, a current vaccine against the hepatitis B virus relies on inoculation using only a portion of the viral surface antigen, rather than the complete pathogen. Vaccines of this type have fewer side-effects, and they avoid the unwanted immune responses to antigens that are non-protective, i.e., do not confer lasting immunity, Vaccines have also been developed using recombinant DNA technology and gene therapy to provide DNA vaccines, which in favorable cases lead to a protective immune response.
[0003] Vaccination with protein antigens (e.g., from a viral protein or a tumorspecific antigen) or immunogenic polypeptides derived from protein antigens is a new strategy that has tremendous clinical potential because of its low toxicity and widespread applicability. Protein-based vaccines, however, have had only limited clinical success, due in part to difficulties with delivery. There is therefore a need to develop more efficacious means of engineering polypeptide-based antigens.
[0004] Currently, synthetic peptide vaccines are being evaluated for protection against bacteria, parasites, and viruses. Bacterial epitope vaccines include those directed against cholera and shigella. A synthetic vaccine against malaria has undergone Phase! and Phase II clinical trials. Influenza and hepatitis B represent two viral systems in which synthetic peptide vaccines look especially promising, and there has been much interest recently in the development of synthetic vaccines against human immunodeficiency virus-1 (HIV-1).
[0005] A desirable immune response to a protein or peptide antigen in a vaccine context includes both humoral and cellular-mediated immunity. The humoral component involves the stimulation of B cells, which produce antibodies, while the cell-mediated component involves T lymphocytes. Cytotoxic T-lymphocytes (CTLs) play an important role in the cell-mediated immune system, lysing virally-infected or bacterially-infected cells. Specifically, CTLs possess cell surface receptors which can recognize foreign peptides associated with MHC class I and/or class H molecules.
[0006] There is a need for methods and specialized delivery platforms suitable for the delivery of complex antigens such as polypeptides to vertebrate organisms. The engineering of immunogenic polypeptides and structures made of immunogenic polypeptides are promising for this purpose. Preferably, the resulting presentation of immunogenic determinants will activate at least some components of the adaptive immune system, i.e., antigen presentation will eliciting a sufficient immune response for combating a particular pathogen, whether the immune response is mediated by antibodies, cytotoxic T cells, helper T cells, natural killer cells, or macrophages, or some combination thereof.
('
SUMMARY
[0007] In one embodiment, an immunogenic composition comprises a multilayer film comprising two or more layers of polyelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes, wherein a first layer polyelectrolye comprises an antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions. The antigenic polypeptide and the one or more surface adsorption regions have the same polarity. The one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per
IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
CROSS-REFERENCE TO RELATED APPLICATION
This application claims the benefit of U.S. Provisional Application No. 60/729,828 filed October 25,2005, which is incorporated by reference herein.
BACKGROUND
[0001] Vaccines have been important in medicine ever since it was observed that, for certain diseases, initial exposure to the infectious agent conferred immunity against subsequent infections. Vaccines have been used for many years in order to build immunity in an individual against infection by particular pathogens such as viruses, bacteria, fungi, and parasites.
Vaccines have also been used to stimulate the body’s ability to mount an immune response against antigens on cancer cells, or against the formation of pathological fibrils. Vaccines can be administered via various routes including, for example, oral, intravenous, subcutaneous, transdermal, sublingual, intramuscular, and nasal administration.
[0002] Early vaccines relied on “live” or “killed pathogens that retained their immunogenicity. A better understanding of the structure and function of particular pathogens and of the mechanisms of adaptive immunity has made it possible to design safer and more directed vaccines. For example, a current vaccine against the hepatitis B virus relies on inoculation using only a portion of the viral surface antigen, rather than the complete pathogen. Vaccines of this type have fewer side-effects, and they avoid the unwanted immune responses to antigens that are non-protective, i.e., do not confer lasting immunity. Vaccines have also been developed using recombinant DNA technology and gene therapy to provide DNA vaccines, which in favorable cases lead to a protective immune response.
[0003] Vaccination with protein antigens (e.g., from a viral protein or a tumor-specific antigen) or immunogenic polypeptides derived from protein antigens is a new strategy that has tremendous clinical potential because of its low toxicity and widespread applicability. Proteinbased vaccines, however, have had only limited clinical success, due in part to difficulties with delivery. There is therefore a need to develop more efficacious means of engineering polypeptide-based antigens.
[0004] Currently, synthetic peptide vaccines are being evaluated for protection against bacteria, parasites, and viruses. Bacterial epitope vaccines include those directed against cholera and shigella. A synthetic vaccine against malaria has undergone Phase I and Phase II clinical trials. Influenza and hepatitis B represent two viral systems in which synthetic peptide vaccines look especially promising, and there has been much interest recently in the development of synthetic vaccines against human immunodeficiency virus-1 (HIV-1).
[0005] A desirable immune response to a protein or peptide antigen in a vaccine context includes both humoral and cellular-mediated immunity. The humoral component involves the stimulation of B cells, which produce antibodies, while the cell-mediated component involves T lymphocytes. Cytotoxic T-lymphocytes (CTLs) play an important role in the cell-mediated immune system, lysing virally-infected or bacterially-infected cells. Specifically, CTLs possess cell surface receptors which can recognize foreign peptides associated with MHC class I and/or class II molecules.
Zheng B et al: Journal of Biomaterials Science Polymer Edition 05, vol. 16, no. 3, March 2005 pages 285-299 describes the principles for selecting charged polypeptides from the human genome, for example, for inclusion in polypeptide multilayer films. Zheng et aL does not disclose a polypeptide layer of a multilayer film that contains an antigenic determinant region.
US 2005/0069950 describes the principles for designing charged polypeptides for inclusion into polypeptide multilayer films. US 2005/0069950 discloses that short peptides should be employed so that an immune response is not introduced. US 2005/0069950 does not disclose a polypeptide layer of a multilayer film that contains an antigenic determinant region.
[0006] There is a need for methods and specialized delivery platforms suitable for the delivery of complex antigens such as polypeptides to vertebrate organisms. The engineering of immunogenic polypeptides and structures made of immunogenic polypeptides are promising for this purpose. Preferably, the resulting presentation of immunogenic determinants will activate at least some components of the adaptive immune system, i.e., antigen presentation will eliciting a sufficient immune response for combating a particular pathogen, whether the immune response is mediated by antibodies, cytotoxic T cells, helper T cells, natural killer cells, or macrophages, or some combination thereof.
SUMMARY
The invention provides an immunogenic composition, comprising a multilayer film comprising two or more layers of polyelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes, wherein a first layer polyelectrolye comprises a first antigenic polypeptide comprising one or more surface
190885# I adsorption regions covalently linked to one or more antigenic determinant regions, wherein, the antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions comprises one or more aminoacid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to 250 amino acid residues, wherein the first antigenic polypeptide is not a homopolymer, is at least 15 amino acids long, and has an aqueous solubility at pH 4 to 10 of greater than 50 pg/rnl, wherein a second layer comprises a second layer polyelectrolyte comprising a polygationic material or a polyanionic material having a molecular weight of greater than 1,0.00 and at least 5 charges per molecule, and a charge opposite that of the first layei polypeptide.
The invention further provides for use of a multilayer film comprising two or moie layers of polvelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes.
wherein a first layer polyelectrolye comprises an antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the antigenic polypeptide and the one or more surface adsorption regions have tire same polarity, wherein the one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to 250 amino acid. residues, wherein the antigenic polypeptide is not a homopolvmer. is at least 15 amino acids long, and has an aqueous solubility' at pH 4 to 10 of greatei than 50pg/ml, wherein a second layer comprises a second layer polyelectrolyte comprising a polycationic material or a polyanionic material having a molecular weight of greater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide, for the preparation of an immunogenic composition for use in a method of eliciting._an immune response in a vertebrate organism wherei n said method comprises administering the immunogenic composition to the vertebrate organism.
The invention further provides a method of makin g an immunogenic composition, the method comprising:
190885^ depositing a first layer polvelectrolyte on a surface of a substrate to form a first layer; wherein, a first layer polyelectrolye comprises a first antigenic polypeptide comprising one 01 more surface adsorption regions covalently linked to one or more antigenic determinant regions, wherein the antigenic polypeptide and the one or more surface adsorption regions have the same polarity, wherein the one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per residue of greater than or equal to 0.4, and wherein the one or more antigenic determinant regions comprises 3 to 250 amino acid residues, wherein the first antigenic polypeptide is not a homopolymer, is at least 15 amino acids long, and has an aqueous solubility at pH 4 to 10 of greater than 50 pg/ml;
depositing a second layer polyelectrolyte on the first layer polyelectrolyte to form a second layer; wherein a second layer comprises a second layer polyelectrolyte comprising^ polycationic material or a polvanionic material having a molecular weight of gieater than 1,000 and at least 5 charges per molecule, and a charge opposite that of the first layer polypeptide.
Notice Under Commissioner's Circular 23/P1 dated April 5,1992
Inasmuch as the invention is defined in the appended claims, it will be apparent that the portions of the present specification, which fall outside the scope of the claims, do not !elate directly to tire claimed invention. This Notice is not meant to disclaim any legitimate lights to which the Patentee is legally entitled, especially any ri ghts in accordance with Section 49 of the
Israel Patent Law.
ADDITIONAL ASPECTS OF THE APPLICATION
[0007] In one embodiment, an immunogenic composition comprises a multilayer film comprising two or more layers of polyelectrolytes, wherein adjacent layers comprise oppositely charged polyelectrolytes, wherein a first layer polyelectrolye comprises an antigenic polypeptide comprising one or more surface adsorption regions covalently linked to one or more antigenic determinant regions. The antigenic polypeptide and the one or more surface adsorption regions have the same polarity. The one or more surface adsorption regions comprises one or more amino acid sequence motifs, the one or more amino acid sequence motifs consisting of 5 to 15 amino acids and having a magnitude of net charge per res idue of greater
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Priority claims8
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| 72982805 | United States of America | P | |
| 2006041666 | United States of America | W | |
| 2006041666 | United States of America | W | |
| 60729828 | – | – | – |
| PCTUS2006041666 | – | – | – |
| US20050729828P | – | – | – |
| WO2006US41666 | – | – | – |
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| US2006205005A1 | United States of America | A1 | |
| US2007077253A1 | United States of America | A1 | |
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| WO2007050702A3 | World Intellectual Property Organization (WIPO) | A3 | |
| US7321022B2 | United States of America | B2 | |
| US2008020402A1 | United States of America | A1 | |
| AU2006347951A1 | Australia | A1 | |
| CA2632703A1 | Canada | A1 | |
| WO2008030253A2 | World Intellectual Property Organization (WIPO) | A2 | |
| US7348399B2 | United States of America | B2 | |
| US2008125575A1 | United States of America | A1 | |
| WO2008030253A3 | World Intellectual Property Organization (WIPO) | A3 | |
| EP1948695A2 | European Patent Office (EPO) | A2 | |
| EP1948696A2 | European Patent Office (EPO) | A2 | |
| US7411038B2 | United States of America | B2 | |
| CN101296945A | China | A | |
| IL190863A0 | Israel | A0 | |
| IL190863D0 | Israel | D0 | |
| IL190885A0 | Israel | A0 | |
| IL190885D0 | Israel | D0 | |
| MX2008005364A | Mexico | A | |
| CN101365724A | China | A | |
| US2009054633A1 | United States of America | A1 | |
| JP2009513651A | Japan | A | |
| JP2009513654A | Japan | A | |
| US7534860B2 | United States of America | B2 | |
| US7538184B2 | United States of America | B2 | |
| US7544770B2 | United States of America | B2 | |
| US7550557B2 | United States of America | B2 | |
| US2009233074A1 | United States of America | A1 | |
| US7615530B2 | United States of America | B2 | |
| US2010028410A1 | United States of America | A1 | |
| US2010028423A1 | United States of America | A1 | |
| US2010028424A1 | United States of America | A1 | |
| US2010028448A1 | United States of America | A1 | |
| US2010034875A1 | United States of America | A1 | |
| US7781399B2 | United States of America | B2 | |
| US7786076B2 | United States of America | B2 | |
| US7807632B2 | United States of America | B2 | |
| US7807633B2 | United States of America | B2 | |
| US7807634B2 | United States of America | B2 | |
| US7893198B2 | United States of America | B2 | |
| EP2308900A2 | European Patent Office (EPO) | A2 | |
| EP2308900A3 | European Patent Office (EPO) | A3 | |
| IL190885AThis record | Israel | A | |
| IL190863A | Israel | A | |
| AU2006306202B2 | Australia | B2 | |
| AU2006347951B2 | Australia | B2 | |
| EP1948695B1 | European Patent Office (EPO) | B1 | |
| DK1948695T3 | Denmark | T3 | |
| ES2400665T3 | Spain | T3 | |
| CN103357007A | China | A | |
| EP2308900B1 | European Patent Office (EPO) | B1 | |
| DK2308900T3 | Denmark | T3 | |
| ES2462519T3 | Spain | T3 | |
| JP5751741B2 | Japan | B2 | |
| CA2627376C | Canada | C | |
| MX345029B | Mexico | B |
5 legal events, as the office reported them to INPADOC
Over the term
Point at a mark for the eventEvents
| Event | Code | |
|---|---|---|
| Patent renewedKB | KB | |
| Patent renewedKB | KB | |
| Patent renewedKB | KB | |
| Patent renewedKB | KB | |
| Patent grantedGrantedFF | FF |
Numbers
- Publication, DOCDB
- 190885
- Publication, EPODOC
- IL190885
- Application
- 190885
- Application, DOCDB
- 19088508
- Application, EPODOC
- IL20080190885
Titles
- English
- IMMUNOGENIC COMPOSITIONS AND METHODS OF USE
Classification
- CPC, 10
- C07K17/00
- A61P31/04
- A61P31/10
- A61P31/12
- A61P31/14
- A61P31/18
- A61P35/00
- A61P37/00
- A61P37/04
- B82Y30/00
