EP4121131A1 - Reactive hydrogel forming formulations and related methods - Google Patents

Reactive hydrogel forming formulations and related methods

Info

Publication number
EP4121131A1
EP4121131A1 EP21719341.6A EP21719341A EP4121131A1 EP 4121131 A1 EP4121131 A1 EP 4121131A1 EP 21719341 A EP21719341 A EP 21719341A EP 4121131 A1 EP4121131 A1 EP 4121131A1
Authority
EP
European Patent Office
Prior art keywords
component
integer
formula
diradical
protein
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
EP21719341.6A
Other languages
German (de)
English (en)
French (fr)
Inventor
Jordan ADDISON
Heather STORM
Ethan BLANK
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Bard Peripheral Vascular Inc
Original Assignee
Bard Peripheral Vascular Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Bard Peripheral Vascular Inc filed Critical Bard Peripheral Vascular Inc
Publication of EP4121131A1 publication Critical patent/EP4121131A1/en
Pending legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
    • A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
    • A61L24/10—Polypeptides; Proteins
    • A61L24/108—Specific proteins or polypeptides not covered by groups A61L24/102 - A61L24/106
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
    • A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
    • A61L24/043—Mixtures of macromolecular materials
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
    • A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
    • A61L24/046—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2400/00—Materials characterised by their function or physical properties
    • A61L2400/06—Flowable or injectable implant compositions
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2430/00—Materials or treatment for tissue regeneration
    • A61L2430/22—Materials or treatment for tissue regeneration for reconstruction of hollow organs, e.g. bladder, esophagus, urether, uterus

Definitions

  • hydrogel tissue sealants are generally described.
  • the subject matter of the present invention involves, in some cases, interrelated products, alternative solutions to a particular problem, and/or a plurality of different uses of one or more systems and/or articles.
  • a hydrogel forming composition for forming a hydrogel tissue sealant is described.
  • the hydrogel forming composition comprises a first component comprising a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula: G-LM-PEG-LM-G; wherein:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • the hydrogel forming composition comprises a second component comprising a protein that is capable of crosslinking with the crosslinking agent.
  • the hydrogel forming composition comprises one or more solvents able to dissolve the first component and the second component, and a surfactant.
  • the first component, the second component, and the surfactant are all dissolved in the one or more solvents, crosslinking of the crosslinking agent and the protein occurs to form the hydrogel tissue sealant.
  • a hydrogel forming composition for forming a hydrogel tissue sealant comprises a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula: G-LM-PEG-LM-G; wherein:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH2) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the
  • the hydrogel forming composition comprises a protein that is capable of crosslinking with the crosslinking agent, one or more solvents able to dissolve the first component and the second component, and a surfactant, wherein when the crosslinking agent, the protein, and the surfactant are all dissolved in the one or more solvents, crosslinking of the crosslinking agent and the protein occurs to form the hydrogel tissue sealant.
  • a hydrogel forming composition for forming a hydrogel tissue sealant comprises a first component comprising a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH2) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the
  • the hydrogel forming composition comprises a second component comprising a protein that is capable of crosslinking with the crosslinking agent and one or more solvents able to dissolve the first component and the second component, wherein when the first component and the second component are dissolved in the one or more solvents, upon mixing of the first component and the second component dissolved in the one or more solvents, crosslinking of the crosslinking agent and the protein occurs with a gel time less than or equal to 20 seconds to form the hydrogel tissue sealant.
  • a hydrogel forming composition for forming a hydrogel tissue sealant comprises a first component comprising a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula —C(O)—, a monoester diradical of the formula —(CH2)b—C(O)— where b is an integer from 1 to 10, a diester radical of the formula —C(O)—(CH 2 ) c —C(O)— where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula —C(O)—O—(CH2)d—O—C(O)— where d is an integer from 1 to 10, an amide containing diradical of the formula —N(H)—C(O)—(CH2)d—C(O)— where d is an integer from 1 to 10, an amide containing diradical of the formula —(CH 2 ) c —C(O) — N(H)
  • the hydrogel forming composition comprises a second component comprising a protein that is capable of crosslinking with the crosslinking agent, a first solvent able to dissolve the first component, and a second solvent able to dissolve the second component, wherein when the second component is dissolved in the second solvent the pH of the solution of the second component in the second solvent is greater than or equal to 10.2 and less than or equal to 10.6, and wherein when the first component is dissolved in the first solvent and combined with the solution of the second component in the second solvent a crosslinking solution of the first component and the second component is formed.
  • a hydrogel forming composition for forming a hydrogel tissue sealant comprises a first component comprising a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula: G-LM-PEG-LM-G; wherein: PEG is polyethylene glycol; each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C
  • the hydrogel forming composition comprise a second component comprising a protein that is capable of crosslinking with the crosslinking agent, and one or more solvents able to dissolve the first component and the second component such that when the first component and the second component are separately mixed with the one or more solvents, at least the second component is able to have a dissolution time at 25 °C of less than or equal to 30 seconds.
  • a method of forming a hydrogel tissue sealant comprises dissolving in a first solvent a first component, wherein the first component comprises a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • the method comprises dissolving in a second solvent a second component, wherein the second component comprises a protein that is capable of crosslinking with the crosslinking agent, and combining the dissolved first component and the dissolved second component to form a hydrogel forming composition comprising the crosslinking agent, the protein, and a surfactant, to initiate crosslinking of the crosslinking agent and the protein, thereby forming the hydrogel tissue sealant.
  • a method of forming a hydrogel tissue sealant comprises dissolving in a first solvent a first component, wherein the first component comprises a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • the method comprises dissolving in a second solvent a second component, wherein the second component comprises a protein that is capable of crosslinking with the crosslinking agent, and combining the dissolved first component and the dissolved second component to form a hydrogel forming composition comprising the crosslinking agent and the protein, thereby initiating crosslinking of the crosslinking agent and the protein to form the hydrogel tissue sealant such that crosslinking is characterized by a gel time less than or equal to 20 seconds.
  • a method of forming a hydrogel tissue sealant comprises dissolving in a first solvent a first component to form a solution of the first component, wherein the first component comprises a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula: G-LM-PEG-LM-G; wherein:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • the method comprises dissolving in a second solvent a second component to form a solution of the second component, wherein the second component comprises a protein that is capable of crosslinking with the cros slinking agent and wherein the solution of the second component has a pH greater than or equal to 10.2 and less than or equal to 10.6, and combining the solution of the first component and the solution of the second component to form a hydrogel forming composition comprising the crosslinking agent and the protein, thereby initiating crosslinking of the crosslinking agent and the protein to form the hydrogel tissue sealant.
  • a method of forming a hydrogel tissue sealant comprises dissolving in a first solvent a first component, wherein the first component comprises a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • the method comprises dissolving in a second solvent a second component, wherein the second component comprises a protein that is capable of crosslinking with the crosslinking agent, wherein the dissolution time of the second component in the second solvent at 25 °C is less than or equal to 30 seconds, and combining the dissolved first component and the dissolved second component to form a hydrogel forming composition comprising the crosslinking agent and the protein, thereby initiating crosslinking of the crosslinking agent and the protein to form the hydrogel tissue sealant.
  • a method of forming a hydrogel tissue sealant comprises forming a hydrogel forming composition comprising a crosslinking agent that is a difunctionalized polyalkylene oxide-based component of the formula:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • the solution comprises a protein that is capable of crosslinking with the crosslinking agent, and a surfactant, wherein the hydrogel forming composition, upon formation, results in initiation of crosslinking of the crosslinking agent and the protein, thereby forming the hydrogel tissue sealant.
  • a method of sealing tissue comprises delivering a hydrogel forming composition to a tissue site, wherein the hydrogel forming composition comprises a reaction product of: a first component comprising a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • a method of sealing tissue comprises delivering a hydrogel forming composition to a tissue site, wherein the hydrogel forming composition is a reaction product of: a solution of a first component comprising a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • a method of sealing tissue comprises delivering a hydrogel forming composition to a tissue site, wherein the hydrogel composition comprises a reaction product of: a first component comprising a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula: G-LM-PEG-LM-G; wherein:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • kits for forming a hydrogel tissue sealant comprising a first component contained within a first container, wherein the first component comprises a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (Clhh — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the
  • a kit for forming a hydrogel tissue sealant comprises a first component in powder form contained within a first container, wherein the first component comprises a crosslinking agent, wherein the crosslinking agent is a difunctionalized polyalkylene oxide-based component of the formula:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • the kit comprises a second component in powder form contained with a second container, wherein the second component comprises a protein that is capable of crosslinking with the crosslinking agent, a first aqueous hydration solution contained within a third container, wherein the first aqueous hydration solution is able to dissolve the first component, and a second aqueous hydration solution contained with a fourth container, wherein the second aqueous hydration solution is able to dissolve the second component.
  • a kit for forming a hydrogel tissue sealant comprises one or more syringes collectively comprising at least three separate containers, wherein a first container comprises a first component in powder form, a second container comprises a second component in powder form, and at least a third container comprises one or more solvents, wherein the one or more syringes are configured such that the first container and the second container are able to be placed in fluid communication with the at least a third container comprising the one or more solvents to facilitate mixing of the first component with the one or more solvents to form a solution of the first component and to facilitate mixing of the second component with the one or more solvents to form a solution of the second component, and wherein the one or more syringes are further configured to mix the solution of the first component and the solution of the second component to form a crosslinking solution of the first component and the second component able to form the hydrogel tissue sealant, wherein the first component comprises an electrophilic biodegradable polymer and the second component comprises
  • a hydrogel forming composition for forming a hydrogel tissue sealant comprises a first component comprising a crosslinking agent which is a difunctionalized polyalkylene oxide-based component of the formula: G-LM-PEG-LM-G; wherein:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • the difunctionalized polyalkylene oxide-based component has the formula G-LM- (OCH 2 CH 2 ) n O-LM-G where n is an integer from 10 to 500, preferably 50 to 200.
  • the leaving group G in the difunctionalized polyalkylene oxide-based component is N-oxysuccinimidyl.
  • the difunctional linking moiety LM in the difunctionalized polyalkylene oxide-based component is selected from — (CH 2 ) b — C(O) — and — C(O) — (CH 2 ) c — C(O) — , wherein b and c are both integers from 1 to 10.
  • the difunctionalized polyalkylene oxide-based component is selected from: wherein in both formulae n is an integer from 10 to 500, preferably 50 to 200.
  • the protein is selected from the group consisting of human serum albumin, recombinant human serum albumin, and animal sourced albumin.
  • the protein is recombinant human serum albumin.
  • the composition further comprises a surfactant dissolved in the one or more solvents.
  • the surfactant is selected from a non-functionalized PEG preferably with a weight average molecular weight of 1000 g/mol to 40000 g/mol, dextran sulfate, a poloxamer, a polysorbate, an oil, a siloxane, a stearate, and/or a glycol.
  • the one or more solvents include water in an amount of 50 wt.% to 100 wt.%, preferably 90 wt.% to 100 wt.%, based on the total amount of solvent.
  • the difunctionalized polyalkylene oxide-based component is selected from: wherein in both formulae n is an integer from 10 to 500, preferably 50 to 200; the protein is recombinant human serum albumin; the surfactant is a non-functionalized PEG; and water makes up 90 wt.% or more of the total amount of the one or more solvents.
  • the composition further comprises a crosslinking initiator, an antioxidant, and/or a radiopaque agent.
  • the composition comprises a base or basic buffer, preferably a carbonate and/or a bicarbonate.
  • the composition comprises an antioxidant, preferably butylated hydroxyanisole, butylated hydroxytoluene, propyl gallate d-alpha tocopheryl polyethylene glycol- 1000 succinate, or sodium metabisulfite, and/or mixtures thereof.
  • an antioxidant preferably butylated hydroxyanisole, butylated hydroxytoluene, propyl gallate d-alpha tocopheryl polyethylene glycol- 1000 succinate, or sodium metabisulfite, and/or mixtures thereof.
  • the composition comprises a radiopaque agent, preferably gold, silver, iodine, potassium chloride, barium sulfate, iohexol, or diatrizoate, and/or mixtures thereof.
  • a first component of the composition is dissolved in a first solvent.
  • a second component of the composition is dissolved in a second solvent.
  • a second component dissolved in the second solvent has a pH of from 10.2 to 10.6.
  • kit for forming a hydrogel tissue sealant comprising: a first container containing a first component comprising the crosslinking agent as defined in this disclosure; a second container containing a second component comprising a protein, preferably a protein selected from the group consisting of human serum albumin, recombinant human serum albumin, and animal sourced albumin; and optionally one or more additional containers containing one or more solvents, preferably water, for dissolving the first component and the second component.
  • a kit comprises a first container containing a first component; a second container containing a second component; and a third container containing a solvent, preferably water, for dissolving the first component and the second component.
  • a kit comprises two syringes, wherein a first syringe comprises a first container and a second container; and wherein a second syringe comprises a third container; wherein a first component and a second component contained in the syringe are in powder form; wherein the first syringe and the second syringe are configured to be fluidically connectable to each other such that the first container and the second container are able to be placed in fluid communication with the third container to facilitate mixing of the first component and the second component with a solvent to form a solution of the first component in the first container and a solution of the second component in the second container, and wherein the first syringe is further configured to mix the solution of the first component and the solution of the second component to form a hydrogel forming composition for forming a hydrogel tissue sealant.
  • such kit comprises a first container containing the first component; a second container containing the second component; a third container containing a solvent, preferably water, for dissolving the first component; and a fourth container containing a solvent, preferably water, for dissolving the second component, and may further comprises two syringes, wherein a first syringe comprises the first container and the second container; and wherein a second syringe comprises the third container and the fourth container; wherein the first component and the second component are in powder form; wherein the first syringe and the second syringe are configured to be fluidically connectable to each other such that the first container and the second container are able to be placed in fluid communication with the third container and the fourth container, respectively, to facilitate mixing of the first component with the solvent in the third container to form a solution of the first component in the first container and to facilitate mixing of the second component with the solvent in the fourth container to form a solution of the second component in the second container, wherein the first syring
  • any hydrogel forming composition described herein, and/or prepared using any kit described herein is suitable for use in a method of treatment by surgery.
  • such method of treatment by surgery includes delivering the hydrogel forming composition to a tissue site and forming a hydrogel tissue sealant at that tissue site.
  • the treatment by surgery is a lung biopsy procedure, and wherein the composition is used to prevent or reduce the risk of pneumothorax during or after the lung biopsy procedure, which can be a procedure wherein any hydrogel forming composition described herein is delivered to the pleural space of the patient to form a hydrogel tissue sealant through which a biopsy sample is taken.
  • a kit for forming a hydrogel tissue sealant comprises a first container containing a first component comprising a crosslinking agent, a second container containing a second component comprising a protein, preferably a protein selected from the group consisting of human serum albumin, recombinant human serum albumin, and animal sourced albumin, and optionally one or more additional containers containing one or more solvents, preferably water, for dissolving the first component and the second component.
  • the hydrogel forming composition as described above or as prepared using the kit as described above may be used in a method of treatment by surgery.
  • FIG. 1 shows, in accordance with certain embodiments, steps in an exemplary method for forming a hydrogel tissue sealant
  • FIG. 2A shows, in accordance with certain embodiments, a schematic diagram of a syringe device that is configured for storing and/or mixing one or more components of the hydrogel forming composition
  • FIG. 2B shows, in accordance with certain embodiments, a schematic diagram of a syringe device that is configured for delivering a hydrogel forming composition to a tissue site;
  • FIG. 3A shows, in accordance with certain embodiments, a cross-sectional schematic diagram of the syringe device shown in FIG. 2A;
  • FIG. 3B shows, in accordance with certain embodiments, a cross-sectional schematic diagram of the syringe device shown in FIG. 2B;
  • FIG. 4 shows, in accordance with certain embodiments, steps in an exemplary method for hydrating and delivering a hydrogel forming composition
  • FIG. 5A shows, in accordance with certain embodiments, a X-ray image of a swine lung model
  • FIG. 5B shows, in accordance with certain embodiments, a X-ray image of a post biopsy swine lung model
  • FIG. 6A shows, in accordance with certain embodiments, a X-ray image of the coaxial insertion of a syringe needle to deliver a hydrogel tissue sealant to a swine lung model;
  • FIG. 6B shows, in accordance with certain embodiments, a X-ray image of swine lung model with a hydrogel tissue sealant
  • FIG. 7A shows, in accordance with certain embodiments, an image of a hydrogel tissue sealant adhered to the parietal pleura of a swine lung model
  • FIG. 7B shows, in accordance with certain embodiments, an image of a hydrogel tissue sealant adhered to the parietal and visceral pleura of swine lung model
  • FIG. 8A shows, in accordance with certain embodiments, a schematic diagram of the syringe device depicted in FIG. 2B having its coaxial cannula inserted into the pleural space of a subject being treated prior to deployment of the hydrogel forming composition contained within the syringe;
  • FIG. 8B shows, in accordance with certain embodiments, a schematic diagram of the syringe device of FIG. 8 A with the plunger depressed for deploying the hydrogel forming composition to deliver and form the hydrogel lung sealant in the pleural space of the subject being treated;
  • FIG. 8C shows, in accordance with certain embodiments, a schematic diagram of a biopsy needle inserted through the coaxial cannula of the syringe device of FIG. 8B;
  • FIG. 9A shows, in accordance with certain embodiments, a CT scan of a test subject (Test Subject 5) three days after deployment of the hydrogel and subsequent lung biopsy procedure
  • FIG. 9B shows, in accordance with certain embodiments, a CT scan of a control subject (Control Subject 9) immediately after a lung biopsy procedure, showing an air embolism
  • FIG. 9C shows, in accordance with certain embodiments, a CT scan of a control subject (Control Subject 10) immediately after a lung biopsy procedure, showing pneumothorax;
  • FIG. 9D shows, in accordance with certain embodiments, a CT scan of a control subject (Control Subject 6) two days after a lung biopsy procedure, showing pneumothorax.
  • a hydrogel forming composition is provided in dry form (e.g. as one or more powder mixtures) and comprises at least a crosslinking agent and a protein that is capable of crosslinking with the crosslinking agent.
  • a solvent i.e., one or more solvents
  • a surfactant that is capable of stabilizing the hydrogel forming composition, increasing the rate of dissolving the protein in the one or more solvents, and/or preventing aggregation of the protein can also be added, either to one or more components of the powder mixture or the one or more solvents.
  • the composition may be segregated into two or more reactive components (e.g. two or more dry powdered mixtures), with at least a first and a second component comprising an ingredient that reacts with one or more ingredients of another of the components.
  • the ingredients in each of the components are not substantially reactive with other ingredients in such component, so that reaction can be prevented until the components are dissolved in one or more suitable solvents (e.g. hydrated) and combined prior to or during use, enabling them to react to form the hydrogel.
  • the components may be formulated and stored in a hydrated, flowable form as opposed to a dry, non-hydrated form.
  • the composition is provided as two dry powder components prior to hydration and mixing of the components to form a crosslinked hydrogel tissue sealant, but as indicated above, other dry and flowable formulations are possible.
  • crosslinking to form the hydrogel tissue sealant may be initiated by combining a first component comprising the crosslinking agent with a second component comprising the protein.
  • the surfactant may be part of the second component.
  • the first component may further include, for example, an antioxidant (e.g., a first antioxidant), which can be selected to increase the stability of the crosslinking agent.
  • the second component may further comprise a second antioxidant, which can be selected to increase the stability of the protein.
  • the hydrogel forming composition can have both an increased shelf-life and enhanced storage capabilities as compared to other conventional hydrogel forming compositions.
  • the hydrogel forming compositions described herein may be stored at room temperature for long periods of time (e.g., three years or more) without requiring refrigeration.
  • Other advantages of the hydrogel forming compositions may include a shorter, tunable gel time, and an increased pot life, both of which are further described below in greater detail.
  • a multicomponent composition formulation may be used.
  • a first component comprises a difunctionalized polyalkylene oxide crosslinking agent
  • a second component comprises a protein (e.g., lyophilized albumin) that is capable of crosslinking with the difunctionalized polyalkylene oxide.
  • the second component may also comprise a crosslinking initiator (e.g., a base or basic buffer, such as sodium carbonate) that initiates crosslinking of the crosslinking agent with the protein.
  • a crosslinking initiator e.g., a base or basic buffer, such as sodium carbonate
  • the first component and the second component may both be provided and stored as powdered mixtures.
  • the powdered mixtures may be separately or concurrently hydrated (e.g., with a solvent, such as water, a biocompatible organic solvent, or an aqueous solution), then combined (if separately hydrated), to form the hydrogel tissue sealant.
  • a solvent such as water, a biocompatible organic solvent, or an aqueous solution
  • the hydrating solution that hydrates the first component (and/or second component) may further comprise a radiopaque agent that permits the hydrogel tissue sealant to be, for example, spectroscopically visible.
  • the hydrating solution that hydrates the second component (and/or first component) may comprise an anti-foaming additive, such as a poloxamer.
  • the anti-foaming additive may assist in refolding of the protein upon hydration.
  • the hydrogel forming composition may be used to bond or seal tissue in vivo.
  • it may be particularly useful to use the hydrogel forming composition as a pleural lung sealant to seal off air or fluid from entering the pleural space.
  • the hydrogel lung sealant may advantageously decrease the occurrence of complications during and/or following the lung biopsy procedure, such as, for example, pneumothorax.
  • compositions and methods described herein may be useful for a variety of other medical applications, such as a postsurgical adhesion barrier or a wound dressing material.
  • crosslink refers to a chemical reaction between two or more similar or dissimilar polymers, copolymers, oligomers, and/or macromers that links the two or more similar or dissimilar polymers, copolymers, oligomers, or macromers via formation of at least one covalent bond and/or ionic bond, or a chain extension between one or more polymers, copolymers, oligomers, and/or macromers to provide a longer chain of the one or more polymers, copolymers, oligomers, and/or macromers via formation of at least one covalent bond and/or ionic bond.
  • the hydrogel forming composition comprises an electrophilic biodegradable polymer.
  • the electrophilic biodegradable polymer may be a synthetic or naturally occurring polymer that contains or is functionalized to contain one or more, and preferably two or more, reactive electrophilic groups.
  • Many suitable electrophilic biodegradable polymers are known to those of ordinary skill in the art.
  • a particularly advantageous and preferred crosslinking agent of the hydrogel forming composition comprises a difunctionalized polyalkylene oxide.
  • the difunctionalized polyalkylene oxide has a composition described by the formula: G-LM-PEG-LM-G; wherein:
  • PEG is polyethylene glycol
  • each LM is a difunctional linking moiety independently selected from the group consisting of a carbonate diradical of the formula — C(O) — , a monoester diradical of the formula — (CH 2 ) b — C(O) — where b is an integer from 1 to 10, a diester radical of the formula — C(O) — (CH 2 ) c — C(O) — where c is an integer from 1 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, a dicarbonate diradical of the formula — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 1 to 10, an amide containing diradical of the formula — N(H) — C(O) — (CH 2 ) d — C(O) — where d is an integer from 1 to 10, an amide containing diradical
  • the crosslinking agent is a difunctionalized polyalkylene oxide of the formula:
  • PEG is polyethylene glycol; each LM is the same and is a difunctional linking moiety represented by the formulas — C(O) — , — (CH 2 ) b — C(O) — where b is an integer from 1 to 5, — C(O) — (CH 2 ) c — C(O) — where c is an integer from 2 to 10 and where the aliphatic portion of the radical may be saturated or unsaturated, — C(O) — O — (CH 2 ) d — O — C(O) — where d is an integer from 2 to 10, and an oligomeric diradical represented by the formulas — R — C(O)— , — R — C(O) — (CH 2 ) c — C(O) — , or — R — C (O) — O — (CH 2 ) d — O — C (O) — where c is an integer from 2 to 10,
  • the hydrogel forming composition comprises any of a variety of suitable crosslinking agents (e.g., difunctionalized polyalkylene oxides).
  • the crosslinking agent is or includes: a 2-arm PEG disuccinimidyl succinate (PEG(SS) 2 ) of the form:
  • the crosslinking agent is or includes: a 2-arm PEG carboxymethyl ester of the form:
  • the crosslinking agent e.g., a difunctionalized polyalkylene oxide
  • the degree of ethoxylation in PEG is such that the crosslinking agent may have a weight average molecular weight of greater than or equal to 1 kDa, greater than or equal to 2 kDa, greater than or equal to 3 kDa, greater than or equal to 4 kDa, greater than or equal to 5 kDa, greater than or equal to 10 kDa, or greater than or equal to 15 kDa.
  • the crosslinking agent may have a weight average molecular weight of less than or equal to 20 kDa, less than or equal to 15 kDa, less than or equal to 10 kDa, less than or equal to 5 kDa, less than or equal to 4 kDa, less than or equal to 3 kDa, or less than or equal to 2 kDa.
  • the crosslinking agent may have a weight average molecular weight of greater than or equal to 1 kDa and less than or equal to 20 kDa, the crosslinking agent may have a weight average molecular weight of greater than or equal to 3 kDa and less than or equal to 5 kDa).
  • n is in the range of 10 to 500, more preferably 50 to 200.
  • the weight average molecular weight of the crosslinking agent is determined using size exclusion chromatography-multi-angle laser light scattering (SEC-MALLS).
  • difunctionalized poly alky lene oxide crosslinking agents describable by the formula G-LM-PEG-LM-G, such as but not limited to the examples noted above, may be prepared by any of a variety suitable synthetic methods known to those skilled in the art. See, for example U.S. Patent 6,576,263, U.S. Patent RE38,827, and U.S. Patent RE38,158, each of which are incorporated herein by reference in its entirety.
  • difunctionalized polyalkylene oxides describable by the formula G-LM-PEG-LM-G may be prepared using known processes, procedures, or synthetic methods such as the procedures reported in U.S. Patent 4,101,380 or U.S.
  • Patent 4,839,345 the procedure reported in International Application Ser. No. PCT/US90/02133 filed Apr. 19, 1990, or the procedure reported by Abuchowski et ah, Cancer Biochem. Biophys., 7:175-186 (1984), each of which are incorporated herein by reference in its entirety.
  • a polyalkylene oxide-based compound e.g., polyethylene glycol discussed below as exemplary
  • a suitable acid anhydride are dissolved in a suitable polar organic solvent in the presence of base and refluxed for a period of time sufficient to form a polyethylene glycol diester diacid.
  • the diester diacid is then reacted with a leaving group, such as a N-hydroxy imide compound, in a suitable polar organic solvent in the presence of dicyclohexylcarbodiimide or another condensing agent, and stirred at room temperature to form the desired difunctional crosslinking agent.
  • a leaving group such as a N-hydroxy imide compound
  • difunctionalized polyalkylene oxide-based compounds describable by the formula G-LM-PEG-LM-G may be purchased from commercial sources, including, but not limited to, NOF America Corporation, Laysan Bio, Inc, Sigma-Aldrich, and/or JenKem Technology USA.
  • the difunctionalized polyalkylene oxide-based compounds may also be readily synthetized by persons of ordinary skill in the chemical synthesis art in view of the teaching and exemplary methods described herein for exemplary compositions, published literature, and the level of ordinary skill and knowledge of the skilled artisan.
  • PEG(SS) 2 can be synthesized by obtaining a linear PEG with an average weight average molecular weight of 3,350 Da, representing 75.7 oxy ethylene repeat units.
  • the linear PEG can be obtained, for example, from Dow Chemical Company.
  • the linear PEG may be converted to PEG(SS) 2 via a two-step synthesis.
  • the first step may comprise reacting the linear PEG with two equivalents of succinic anhydride to form an ester.
  • the second step may comprise reacting the ester with two equivalents of the N- hydroxysuccinimide (NHS) to produce the crosslinking agent PEG(SS) 2 , resulting in a white solid of a 2-arm crosslinking agent that possesses two succinimidyl groups per molecule.
  • NHS N- hydroxysuccinimide
  • difunctionalized poly alky lene oxide-based compounds of the formula G-LM-PEG-LM-G comprise a leaving group G (e.g., N-oxysuccinimidyl, N-oxymaleimidyl, N-oxyphthalimidyl, nitrophenoxyl, N-oxyimidazolyl, and tresyl).
  • leaving group G is an electrophilic leaving group that is capable of reacting with a nucleophilic group, for example an amine group of a protein.
  • the leaving group G reacts with an amine group of the nucleophile (e.g., protein) to produce a crosslinked composition by formation of amide bonds upon release of the leaving group G.
  • nucleophile e.g., protein
  • the purity of the difunctionalized polyalkylene oxide crosslinking agent may be determined by its percent difunctionality.
  • a high percentage of difunctionality may advantageously result in a higher degree and/or rate of crosslinking to provide the a hydrogel formed from the hydrogel forming composition with enhanced performance characteristics, such as a fast gel time, a longer pot life, and/or a longer shelf life, and/or improved mechanical properties or resorption time, each of which are explained below in greater detail.
  • the difunctionalized polyalkylene oxide crosslinking agent has a percent difunctionality greater than or equal to 75 wt.%, greater than or equal to 80 wt.%, greater than or equal to 85 wt.%, greater than or equal to 90 wt.%, greater than or equal to 95 wt.%, or greater than or equal to 99 wt.%. In certain embodiments, the difunctionalized polyalkylene oxide crosslinking agent has a percent difunctionality between 70 wt.% and 99.9 wt.%, or between 90 wt.% and 95%. Other ranges are also possible. The percent difunctionality of the difunctionalized polyalkylene oxide crosslinking agent as used herein is determined by high-performance liquid chromatography (HPLC).
  • the difunctionalized polyalkylene oxide crosslinking agent may have a relatively low weight percent moisture content.
  • a low weight percent moisture content for the powdered difunctionalized polyalkylene oxide crosslinking agent can advantageously provide a hydrogel forming composition with an improved shelf life, as hydrolysis of the difunctionalized polyalkylene oxide is reduced, therefore preserving reactivity of the crosslinking agent over storage time.
  • the weight percent moisture content of the powdered difunctionalized polyalkylene oxide crosslinking agent may be less than or equal to 10 wt.%, less than or equal to 9 wt.%, less than or equal to 8 wt.%, less than or equal to 7 wt.%, less than or equal to 6 wt.%, less than or equal to 5 wt.%, less than or equal to 4 wt.%, less than or equal to 3 wt.%, or less than or equal to 2 wt.% based on the total weight of the powdered difunctionalized polyalkylene oxide crosslinking agent.
  • the weight percent moisture content of the powdered crosslinking agent may be between 1 wt.% and 10 wt.% based on the total weight of the powdered difunctionalized polyalkylene oxide crosslinking agent, or between 4 wt.% and 6 wt.% based on the total weight of the powdered difunctionalized polyalkylene oxide crosslinking agent. Other ranges are also possible.
  • the weight percent moisture content as stated herein is determined using a moisture analyzer and/or a Karl-Fischer titration.
  • the hydrogel forming composition comprises the powdered crosslinking agent in any of a variety of suitable amounts in weight percent (wt.%) by mass versus the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the crosslinking agent in an amount, on a powdered basis, greater than or equal to 10 wt.%, greater than or equal to 15 wt.%, greater than or equal to 20 wt.%, greater than or equal to 25 wt.%, greater than or equal to 30 wt.%, greater than or equal to 35 wt.%, greater than or equal to 40 wt.%, greater than or equal to 45 wt.%, greater than or equal to 50 wt.%, or greater than or equal to 55 wt.% of the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the crosslinking agent, on a powdered basis, in an amount less than or equal to 60 wt.%, less than or equal to 55 wt.%, less than or equal to 50 wt.%, less than or equal to 45 wt.%, less than or equal to 40 wt.%, less than or equal to 35 wt.%, less than or equal to 30 wt.%, less than or equal to 25 wt.%, less than or equal to 20 wt.%, or less than or equal to 15 wt.% of the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the crosslinking agent in an amount, on a powdered basis, greater than or equal to 10 wt.% and less than or equal to 60 wt.% of the total weight of the powdered hydrogel forming composition
  • the hydrogel forming composition comprises the crosslinking agent in an amount, on a powdered basis, greater than or equal to 25 wt.% and less than or equal to 30 wt.% of the total weight of the powdered hydrogel forming composition.
  • Other ranges are also possible.
  • the hydrogel forming composition comprises a nucleophilic biodegradable polymer that is able to crosslink with the electrophilic biodegradable polymer.
  • the nucleophilic biodegradable polymer may be a synthetic or naturally occurring polymer that contains or is functionalized to contain one or more, and preferably two or more, reactive nucleophilic groups.
  • Many suitable nucleophilic biodegradable polymers are known to those of ordinary skill in the art.
  • a particularly advantageous and preferred nucleophilic biodegradable polymer is a protein.
  • the hydrogel forming composition comprises a protein that is capable of crosslinking with the above described electrophilic crosslinking agents (e.g., PEG(SS) 2 ).
  • the protein comprises serum albumin (SA).
  • SA serum albumin
  • the serum albumin may be, in some embodiments, human serum albumin (HSA) derived from donor blood, recombinant human serum albumin (rHSA) expressed in yeast and/or rice, and/or animal sourced albumin, such as, for example, bovine serum albumin (BSA).
  • the protein e.g., rHSA
  • the protein may be lyophilized. Lyophilization of the protein may advantageously impede the degradation of the protein and improve shelf life and/or dissolution time when dissolved in an aqueous solvent, as described below, according to some embodiments.
  • the protein may be Cohn analog culture grade BSA obtained from Proliant Biologicals.
  • the recombinant human serum albumin may be Cellastim recombinant human serum albumin, Healthgen recombinant human serum albumin, Optibumin recombinant human serum albumin, InVitria human serum albumin, or Albumedix human serum albumin.
  • the protein may be or include collagen or gelatin. Other proteins are also possible.
  • the purity and/or amount of protein aggregation may be determined by the percent of the amount of monomer of the protein in the protein source.
  • the protein may comprise greater than or equal to 60 wt.% protein monomer, greater than or equal to 65 wt.% protein monomer, greater than or equal to 70 wt.% protein monomer, greater than or equal to 75 wt.% protein monomer, greater than or equal to 80 wt.% protein monomer, greater than or equal to 85 wt.% protein monomer, greater than or equal to 90 wt.% protein monomer, or greater than or equal to 95 wt.% protein monomer.
  • the protein comprises less than or equal to 99 wt.% protein monomer, less than or equal to 95 wt.% protein monomer, less than or equal to 90 wt.% protein monomer, less than or equal to 85 wt.% protein monomer, less than or equal to 80 wt.% protein monomer, less than or equal to 75 wt.% protein monomer, less than or equal to 70% protein monomer, less than or equal to 70 wt.% protein monomer, or less than or equal to 65 wt.% protein monomer.
  • the protein comprises greater than or equal to 60 wt.% protein monomer and less than or equal to 99 wt.% protein monomer, the protein comprises greater than or equal to 90 wt.% protein monomer and less than or equal to 95 wt.% protein monomer).
  • certain components of the hydrogel forming composition e.g., the surfactant and/or anti- foaming agent may act to prevent aggregation and/or the formation of protein dimers or higher order multimeric structures.
  • the powdered protein may have a relatively low weight percent moisture content.
  • the weight percent moisture content of the powdered protein component may be greater than or equal to 1 wt.%, greater than or equal to 2 wt.%, greater than or equal to 3 wt.%, greater than or equal to 4 wt.%, greater than or equal to 5 wt.%, greater than or equal to 6 wt.%, greater than or 7 wt.%, greater than or equal to 8 wt.%, or greater than or equal to 9 wt.% versus the total weight of the powdered protein component.
  • the weight percent of moisture content of the powdered protein may be less than or equal to 10 wt.%, less than or equal to 9 wt.%, less than or equal to 8 wt.%, less than or equal to 7 wt.%, less than or equal to 6 wt.%, less than or equal to 5 wt.%, less than or equal to 4 wt.%, less than or equal to 3 wt.%, or less than or equal to 2 wt.% versus the total weight of the powdered protein component.
  • the percent moisture content of the powdered protein may be between greater than or equal to 1 wt.% and less than or equal to 10 wt.% versus the total weight of the powdered protein component
  • the percent moisture content of the powdered protein may be between greater than or equal to 4 wt.% and less than or equal to 6 wt.% versus the total weight of the powdered protein component.
  • Other ranges are also possible.
  • the weight percent of moisture content is determined using a moisture analyzer and/or a Karl-Fischer titration.
  • an overall powdered hydrogel forming composition comprises the protein (e.g., albumin) in any of a variety of suitable amounts in weight percent (wt.%) by mass versus the total weight of the powdered hydrogel forming composition (i.e., based on the combined weight of both the protein containing powdered component and the electrophilic polymer containing crosslinking agent powdered component).
  • protein e.g., albumin
  • wt.% weight percent
  • the hydrogel forming composition comprises the protein in an amount, on a powdered basis, greater than or equal to 40 wt.%, greater than or equal to 45 wt.%, greater than or equal to 50 wt.%, greater than or equal to 55 wt.%, greater than or equal to 60 wt.%, greater than or equal to 65 wt.%, greater than or equal to 70 wt.%, or greater than or equal to 75 wt.% of the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the protein, on a powdered basis, in an amount of less than or equal to 80 wt.%, less than or equal to 75 wt.%, less than or equal to 70 wt.%, less than or equal to 65 wt.%, less than or equal to 60 wt.%, less than or equal to 55 wt.%, less than or equal to 50 wt.%, or less than or equal to 45 wt.% of the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the protein in an amount, on a powdered basis, greater than or equal to 40 wt.% and less than or equal to 80 wt.% of the total weight of the powdered hydrogel forming composition
  • the hydrogel forming composition comprises the protein in an amount, on a powdered basis, greater than or equal to 55 wt.% and less than or equal to 65 wt.% of the total weight of the powdered hydrogel forming composition.
  • Other ranges are also possible.
  • the ratio of the leaving group G (e.g., NHS) in the difunctionalized polyalkylene oxide-based compound of the formula G-LM-PEG-LM-G to the number of amine groups (e.g., of the protein) can be any of variety of suitable ratios.
  • the ratio of the leaving group G to the amine groups is greater than or equal to 0.5:1, greater than or equal to 1:1, greater than or equal to 1.5:1, greater than or equal to 2:1, or greater than or equal to 2.5:1.
  • the ratio of the leaving group G to the amine groups is less than or equal to 3:1, less than or equal to 2.5:1, less than or equal to 2:1, less than or equal to 1.5:1, or less than or equal to 1:1.
  • the crosslinking agent is PEG(SS) 2 and the protein is rHSA, and the ratio of NHS groups of PEG(SS) 2 to amine groups of rHSA is 2.21:1. In other non-limiting embodiments, the crosslinking agent is PEG(SS) 2 and the protein is rHSA, and the ratio of NHS groups of PEG(SS) 2 to amine groups of rHSA is 2.65:1.
  • the crosslinking reactions that occur between the electrophilic crosslinking agent and the nucleophile are pH sensitive. In certain such embodiments, for example, the crosslinking reactions are inhibited at acidic pH and can be initiated and sustained by increasing the pH to neutral or basic values.
  • the hydrogel forming composition comprises a crosslinking initiator that initiates crosslinking of the crosslinking agent with the nucleophile (e.g., protein).
  • the crosslinking initiator may be combined as a powder mixture with the protein. In some such embodiments, the crosslinking initiator may be lyophilized with the protein.
  • the crosslinking initiator may be, in some embodiments, a base or a basic buffer.
  • the crosslinking initiator comprises a base and/or basic buffer that facilitates the reaction between the leaving group G in a difunctionalized polyalkylene oxide-based compound of the formula G- LM-PEG-LM-G and the amine group of a protein. Any of a variety of suitable bases or basic buffers may be utilized.
  • the basic crosslinking initiator is a base and/or basic buffer that does not include amine functionalities.
  • the base comprises a carbonate and/or a bicarbonate (e.g., a carbonate and/or a bicarbonate salt).
  • the base or basic buffer comprises sodium carbonate.
  • the base or basic buffer comprises sodium bicarbonate.
  • Other bases or basic buffers are possible.
  • the crosslinking reaction between the leaving group G and the amine group of the nucleophile may occur at any of a variety of suitable pH values. In some embodiments, the crosslinking reaction is favored at high pH values. In certain embodiments, for example, the crosslinking reaction between the leaving group G and the amine group of the nucleophile (e.g., protein) is initiated and occurs at a pH greater than or equal to7, greater than or equal to 8, greater than or equal to 9, greater than or equal to 10, or greater than or equal to 11.
  • the crosslinking reaction between the leaving group G and the amine group of the nucleophile is initiated and occurs at a pH less than or equal to 12, less than or equal to 11, less than or equal to 10, or less than or equal to 9. Combinations of the above recited ranges are also possible (e.g., the crosslinking reaction between the leaving group G and the amine group of the nucleophile is initiated and occurs at a pH between greater than or equal to 7 and less than or equal to 11, the crosslinking reaction between the leaving group G and the amine group of the nucleophile is initiated and occurs at a pH between greater than or equal to 8 and less than or equal to 11, the crosslinking reaction between the leaving group G and the amine group of the nucleophile is initiated and occurs at a pH between greater than or equal to 9 and less than or equal to 11, or the crosslinking reaction between the leaving group G and the amine group of the nucleophile is initiated and occurs at a pH between greater than or equal to 10 and less than or equal to 11. Other ranges are
  • the crosslinking reaction between the leaving group G and the amine group of the nucleophile can be initiated to occur at a pH suitable for facilitating reaction by combining a solution of the crosslinking agent with a solution of the nucleophile, wherein the pH of the solution of the nucleophile is between greater than or equal to 10.2 and less than or equal to 10.6.
  • the hydrogel forming composition may comprise the powdered crosslinking initiator (e.g., base or basic buffer) in any of a variety of suitable amounts in weight percent (wt.%) by mass based on the total weight of the powdered hydrogel forming composition.
  • the amount of the base or basic buffer may affect the reactivity of the hydrogel forming composition, such as the gel time (described below), or other measure of the time it takes for the crosslinking agent to crosslink with the nucleophile (e.g., protein).
  • the hydrogel forming composition comprises the crosslinking initiator in an amount, on a powdered basis, greater than or equal to 0.1 wt.%, greater than or equal to 0.2 wt.%, greater than or equal to 0.5 wt.%, greater than or equal to 1 wt.%, greater than or equal to 1.5 wt.%, greater than or equal to 2 wt.%, greater than or equal to 2.5 wt.%, greater than or equal to 3 wt.%, greater than or equal to 4 wt.%, or greater than or equal to 5 wt.%, greater than or equal to 6 wt.%, greater than or equal to 7 wt.%, greater than or equal to 8 wt.%, or greater than or equal to 9 wt.% of the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the crosslinking initiator in an amount, on a powdered basis, less than or equal to 10 wt.%, less than or equal to 9 wt.%, less than or equal to 8 wt.%, less than or equal to 6 wt.%, less than or equal to 5 wt.%, less than or equal to 4 wt.%, less than or equal to 3 wt.%, less than or equal to 2 wt.%, less than or equal to 1.5 wt.%, less than or equal to 1 wt.%, less than or equal to 0.5 wt.%, or less than or equal to 0.2 wt.%, or less than or equal to 5 wt.% of the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the crosslinking initiator in an amount, on a powdered basis, greater than or equal to 0.1 wt.% and less than or equal to 10 wt.% of the total weight of the powdered hydrogel forming composition or greater than or equal to 0.1 wt.% and less than or equal to 5 wt.% of the total weight of the powdered hydrogel forming composition
  • the hydrogel forming composition comprises the crosslinking initiator in an amount, on a powdered basis, greater than or equal to 4 wt.% and less than or equal to 8 wt.% of the total weight of the composition.
  • Other ranges are also possible.
  • the crosslinking initiator may be compartmentalized to be part of the second component.
  • the crosslinking initiator may be combined with the protein (e.g., albumin) as a powder mixture.
  • the crosslinking initiator and the protein may be lyophilized.
  • the crosslinking initiator may be dissolved in a solvent (e.g., water) and used as the hydration solution to hydrate the second component (e.g., the protein).
  • the hydrogel forming composition comprises a surfactant.
  • the surfactant is capable of stabilizing one or more components (e.g., the first component, the second component) of the hydrogel forming composition.
  • the surfactant is capable of increasing the rate of dissolution of the protein (e.g., albumin) in one or more solvents used to dissolve the protein.
  • the surfactant may be selected to prevent aggregation (e.g., clumping) of the protein (e.g., albumin).
  • the surfactant comprises a non-functionalized polyethylene glycol (PEG).
  • PEG polyethylene glycol
  • the non-functionalized PEG will be a solid at room temperature.
  • the non-functionalized PEG will have a weight average molecular weight, for example, greater than or equal to 100 g/mol and less than or equal to 40,000 g/mol.
  • the non-functionalized PEG is PEG 8000 (e.g., a PEG with a molecular weight of 8000 g/mol).
  • the surfactant comprises dextran sulfate.
  • the surfactant may comprise a poloxamer, a polysorbate (e.g., TWEEN®), or encompass a purely lipophilic material such as an oil (e.g., mineral oil, vegetable oil), a siloxane, a stearate, a glycol, and/or mixtures thereof.
  • the poloxamer is Pluronic® L61. Other Pluronic® poloxamers may be also utilized.
  • the surfactant may additionally function as an anti- foaming additive (although not all anti-foaming additives need to be surfactants).
  • the anti-foaming additive may advantageously prevent foaming and/or air bubbles from forming when the hydrogel forming composition is hydrated to facilitate crosslinking.
  • the anti-foaming additive prevents the formation of air bubbles that would otherwise be present in the hydrated hydrogel forming composition if an anti-foaming additive were not present. Such air bubbles may disrupt crosslinking and weaken the resulting hydrogel network of the tissue sealant.
  • a poloxamer e.g., Pluronic® L61 is an anti-foaming additive.
  • the hydrogel forming composition comprises the powdered or liquid surfactant in any of a variety of amounts in weight percent (wt.%) by mass versus the total weight of the powdered or aqueous solution of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the surfactant in an amount, on a powdered or liquid basis, greater than or equal to 0.01 wt.%, greater than or equal to 0.1 wt.%, greater than or equal to 0.5 wt.%, greater than or equal to 1 wt.%, greater than or equal to 5 wt.%, greater than or equal to 10 wt.%, or greater than or equal to 15 wt.% of the total weight of the powdered or aqueous hydrogel forming composition.
  • the hydrogel forming composition comprises the surfactant, on a powdered or liquid basis, in an amount less than or equal to 20 wt.%, less than or equal to 15 wt.%, less than or equal to 10 wt.%, less than or equal to 5 wt.%, less than or equal to 1 wt.%, less than or equal to 0.5 wt.%, less than or equal to 0.1 wt.%, less than or equal to 0.01 wt.% of the total weight of the powdered or aqueous hydrogel forming composition.
  • the hydrogel forming composition comprises the surfactant in an amount, on a powdered or liquid basis, greater than or equal to 1 wt.% and less than or equal to 30 wt.% of the total weight of the powdered or aqueous hydrogel forming composition
  • the hydrogel forming composition comprises the surfactant in an amount, on a powdered or liquid basis, greater than or equal to 10 wt.% and less than or equal to 20 wt.% of the total weight of the powdered or aqueous solution of the powdered hydrogel forming composition.
  • Other ranges are also possible.
  • the surfactant may be a part of the second component.
  • the surfactant may be combined with the protein (and the crosslinking initiator, in some embodiments) as a powder mixture.
  • the protein, crosslinking initiator, and surfactant may be lyophilized (e.g., prior to dissolution in the solvent).
  • a liquid surfactant e.g., Pluronic® L61
  • the liquid surfactant may hydrogen bond with one or more powder components of the second component (e.g., the protein).
  • the surfactant may be dissolved in and/or mixed with a solvent (e.g., water) that is used as a hydration solution to hydrate the second component to form a hydrated solution that is capable of crosslinking with the first component when mixed with a solution of the first component.
  • a solvent e.g., water
  • the surfactant may be dispersed and/or suspended in a solvent used to hydrate the second component.
  • the hydrogel forming composition may comprise more than one surfactant (e.g., two surfactants, three surfactants, etc.), with each individual surfactant, or the cumulative amount of all the surfactants together falling in any of the weight percent ranges listed above.
  • more than one surfactant e.g., two surfactants, three surfactants, etc.
  • the hydrogel forming composition may comprise at least one antioxidant.
  • An antioxidant may advantageously increase the storage stability of one or more components of the hydrogel forming composition.
  • the use of one or more antioxidants may increase the shelf-life and/or storage capabilities of the hydrogel forming composition. Because the one or more antioxidants are more susceptible to oxidation than the crosslinking reagents for forming the hydrogel (e.g., due to a lower oxidation potential), the antioxidants become oxidized during storage prior to the crosslinking reagents, resulting in a hydrogel forming composition that has a longer shelf-life than a hydrogel forming composition that is otherwise comparable but does not have the one or more antioxidants.
  • the composition comprises butylated hydroxytoluene (BHT).
  • BHT prevents free radical-mediated oxidation.
  • BHT may be utilized to prevent oxidation of the difunctionalized polyalkylene oxide-based crosslinking agent.
  • the composition comprises N-acetyl-DL-tryptophan.
  • N-acetyl-DL- tryptophan prevents oxidation of one or more amino acids and/or other residues of the protein.
  • the antioxidant is or comprises butylated hydroxyanisole, butylated hydroxytoluene, propyl gallate d-alpha tocopheryl polyethylene glycol- 1000 succinate, sodium metabisulfite, and/or mixtures thereof.
  • the hydrogel forming composition comprises at least two antioxidants.
  • the hydrogel forming composition may comprise a first antioxidant (e.g., BHT) to prevent oxidation of the difunctionalized polyalkylene oxide-based crosslinking agent and a second antioxidant (e.g., N-acetyl- DL-tryptophan) to prevent oxidation of the protein.
  • a first antioxidant e.g., BHT
  • a second antioxidant e.g., N-acetyl- DL-tryptophan
  • the one or more antioxidants can in some cases stabilize one or more ingredients of the hydrogel forming composition (e.g., the crosslinking agent, the protein, etc.) to allow sterilization with a lethal dose of radiation (e.g., electron beam or gamma radiation).
  • a lethal dose of radiation e.g., electron beam or gamma radiation
  • one or more components of the hydrogel forming composition may be sterilized using electron beam radiation.
  • the one or more components of the hydrogel may be exposed to one or more doses of electron beam radiation with a cumulative dose between greater than or equal to 25 kGy and less than or equal to 30 kGy.
  • the hydrogel forming composition comprises each antioxidant (e.g., a first antioxidant, a second antioxidant) in any of a variety of suitable amounts in weight percent (wt.%) by mass versus the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises each antioxidant in an amount, on a powdered basis, greater than or equal to 0.1 wt%, greater than or equal to 1 wt.%, greater than or equal to 2 wt.%, greater than or equal to 5 wt.%, greater than or equal to 10 wt.%, or greater than or equal to 15 wt.% of the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises each antioxidant in an amount, on a powdered basis, less than or equal to 20 wt.%, less than or equal to 15 wt.%, less than or equal to 10 wt.%, less than or equal to 5 wt.%, less than or equal to 2 wt.%, less than or equal to 1 wt.%, or less than or equal to 0.1 wt.% of the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises each antioxidant in an amount, on a powdered basis, greater than or equal to 0.1 wt.% and less than or equal to 20 wt.% of the total weight of the powdered hydrogel forming composition
  • the hydrogel forming composition comprises each antioxidant in an amount, on a powdered basis, greater than or equal to 1 wt.% and less than or equal to 5 wt.% of the total weight of the powdered hydrogel forming composition.
  • Other ranges are also possible.
  • the antioxidant may be a part of the first and/or second component.
  • at least one antioxidant may be combined with the crosslinking agent and/or protein as a powder mixture.
  • the antioxidant may by lyophilized with the protein (and/or the crosslinking agent, in some cases).
  • the antioxidant may be dissolved (e.g., in a solvent such as water) that is used as the hydration solution to hydrate the first and/or second component.
  • the hydrogel forming composition comprises a radiopaque agent.
  • a radiopaque agent can provide the resulting hydrogel with the ability to be spectroscopically imaged, for example, by X-ray or computed tomography (CT) imaging. Any of a variety of suitable radiopaque agents may be added.
  • the radiopaque agent comprises gold (e.g., gold nanoparticles), silver (e.g., silver nanoparticles), or iodine.
  • the radiopaque agent is potassium chloride (KC1), barium sulfate, iohexol, or diatrizoate.
  • the hydrogel forming composition comprises the radiopaque agent in any of a variety of amounts in weight percent (wt.%) by mass versus the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the radiopaque agent in an amount, on a powdered basis, greater than or equal to 0.1 wt.%, greater than or equal to 0.5 wt.%, greater than or equal to 1 wt.%, greater than or equal to 5 wt.%, greater than or equal to 10 wt.%, or greater than or equal to 15 wt.% of the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the radiopaque agent, on a powdered basis, in an amount less than or equal to 20 wt.%, less than or equal to 15 wt.%, less than or equal to 10 wt.%, less than or equal to 5 wt.%, less than or equal to 1 wt.%, or less than or equal to 0.5 wt.% of the total weight of the powdered hydrogel forming composition.
  • the hydrogel forming composition comprises the radiopaque agent in an amount, on a powdered basis, greater than or equal to 0.1 wt.% and less than or equal to 20 wt.% of the total weight of the powdered hydrogel forming composition
  • the hydrogel forming composition comprises the radiopaque agent in an amount, on a powdered basis, greater than or equal to 1 wt.% and less than or equal to 10 wt.% of the total weight of the powdered hydrogel forming composition.
  • Other ranges are also possible.
  • the hydrogel forming composition may comprise other active agents or ingredients for various purposes, for example any of a variety of suitable active agents, such as antimicrobials, anti-inflammatories, hemostatic agents, etc.
  • the hydrogel forming composition is in the form of one or more powders (e.g., during storage of the hydrogel forming composition).
  • the one or more powders of the hydrogel forming composition may be hydrated with water or one or more aqueous solutions in order to form an aqueous solution of the hydrogel forming composition comprising the crosslinking agent, the protein, the optional surfactant(s), the optional antioxidant(s), and/or the optional crosslinking initiator(s).
  • forming the aqueous solution form of the hydrogel forming composition comprising the crosslinking agent and the protein initiates crosslinking of the crosslinking agent and the protein, thereby forming a hydrogel tissue sealant.
  • the hydrogel forming composition may be stored and/or provided as a multicomponent formulation where certain of the ingredients are segregated from others in different powdered or hydrated components.
  • the hydrogel forming composition comprises at least a first component, a second component, a solvent able to dissolve the first component and the second component, and, optionally, a surfactant.
  • the first component comprises the crosslinking agent and an optional antioxidant
  • the second component comprises the protein.
  • the surfactant in certain embodiments, may be a part of the second component (e.g., a powder mixture with the protein), or may be dissolved in and/or otherwise mixed with a solvent that is used to hydrate the first and/or second components.
  • the hydrogel forming composition comprises a crosslinking initiator, which may be a part of the second component (e.g., a powder mixture with the protein), or may be dissolved in a solvent that is used to hydrate one or the components (e.g., the second component).
  • the second component is a mixture (e.g., a lyophilized powder mixture) including the protein, the crosslinking initiator, and the surfactant.
  • the hydrogel forming composition may also comprise at least one antioxidant, in some embodiments, which may be a part of the first and/or second component, or may be dissolved in a solvent that is used to hydrate the first and/or second component.
  • the hydrogel forming composition may also comprise a radiopaque agent, in some embodiments, which may be a part of the first and/or second component, or may be dissolved in a solvent that is used to hydrate the first and/or second component.
  • the first component e.g., comprising the crosslinking agent (and optional antioxidant)
  • the second component e.g., comprising the protein (and optionally a crosslinking initiator and/or surfactant)
  • at least the second component comprising the protein, the crosslinking initiator, and the surfactant may be lyophilized, or at least the protein of such component is lyophilized.
  • the first component may be in the form of a first powder mixture and the second component may be in the form of a second powder mixture (e.g., during storage of the first component and/or the second component).
  • the first component and/or the second component that are powder mixtures may be separately solvated or hydrated (in the description below, “hydrated” is used for brevity, but it should be understood that for embodiments where a non-aqueous solvent is used, “solvated” should be substituted for “hydrated”) with water or one or more solvents (e.g., water, biocompatible organic solvent such as DMSO) or aqueous solutions, thereby providing a first component that is in the form of a first solution (e.g., first aqueous solution) and a second component that is in the form of a second solution (e.g., second aqueous solution).
  • a first solution e.g., first aqueous solution
  • a second component that is in the form of a second solution
  • the first component e.g., the crosslinking agent
  • a biocompatible organic solvent such as DMSO
  • the hydrated first component and the hydrated second component may be combined in order to initiate crosslinking of the crosslinking agent and the protein, thereby forming the hydrogel tissue sealant.
  • the first solution (e.g., that hydrates the first component comprising the crosslinking agent) may comprise the radiopaque agent and/or the first antioxidant.
  • the second solution (e.g., that hydrates the second component comprising the protein) may comprise the surfactant, the crosslinking initiator, and/or the second antioxidant.
  • the second component when a protein is included as the nucleophilic polymer, may be hydrated such that the concentration of the protein in the resulting hydrated solution is any of a variety of suitable amounts.
  • the concentration of the protein in the hydrated second component is greater than or equal to 10% mass by volume, greater than or equal to 15% mass by volume, greater than or equal to 20% mass by volume, greater than or equal to 25% mass by volume, or greater than or equal to 30% mass by volume. In certain embodiments, the concentration of the protein in the hydrated second component is less than or equal to 35% mass by volume, less than or equal to 30% mass by volume, less than or equal to 25% mass by volume, less than or equal to 20% mass by volume, or less than or equal to 15% mass by volume.
  • the concentration of the protein in the hydrated second component is greater than or equal to 10% mass by volume and less than or equal to 35% mass by volume, the concentration of the protein in the hydrated second component is greater than or equal to 20% mass by volume and less than or equal to 25% mass by volume).
  • Other ranges are also possible.
  • the lyophilized second component comprising the protein may have a relatively fast dissolution time.
  • dissolution time is given its ordinary meaning in the art and generally refers to the time it takes for the second component comprising the protein to completely dissolve when hydrated (or solvated) with mixing or agitation.
  • a relatively fast dissolution time may advantageously reduce the time it takes to form the hydrogel tissue sealant. The dissolution time is calculated by starting a timer, hydrating the second component by mixing the second component and the hydration solution, and stopping the timer when the second component is completely dissolved.
  • the dissolution time of the second component at 25 °C may be greater than or equal to 10 seconds, greater than or equal to 15 seconds, greater than or equal to 20 seconds, greater than or equal to 25 seconds, greater than or equal to 30 seconds, or greater than or equal to 35 seconds. In certain embodiments, the dissolution time of the second component at 25 °C is less than or equal to 40 seconds, less than or equal to 35 seconds, less than or equal to 30 seconds, less than or equal to 25 seconds, less than or equal to 20 seconds, or less than or equal to 15 seconds.
  • the dissolution time of the second component at 25 °C is between greater than or equal to 10 seconds and less than or equal to 40 seconds
  • the dissolution time of the second component at 25 °C is between greater than or equal to 20 seconds and less than or equal to 30 seconds.
  • Other ranges are also possible.
  • the dissolution time of the second component may depend on the amount of protein in the second component upon hydration, i.e. its mass by volume of the solution.
  • the dissolution time of the second component is directly proportional to the amount of protein in the second component.
  • a second component comprising a relatively low amount of protein e.g., 10% mass by volume in the resulting hydration solution
  • a relatively high amount of protein e.g. 30% mass by volume in the resulting hydration solution
  • the solution of the lyophilized second component may have a relatively high pH upon dissolution.
  • the solution of the lyophilized second component, upon dissolution has a pH greater than or equal to 9, greater than or equal to 9.5, greater than or equal to 10, or greater than or equal to 10.5.
  • the solution of the lyophilized second component, upon dissolution has a pH less than or equal to 11, less than or equal to 10.5, less than or equal to 10, or less than or equal to 9.5.
  • the amount of protein added need not be specified, so long as there exists an amount of the protein that can be hydrated to produce such a pH. That said, in some embodiments, dissolution of even a relatively small amount of the second component (e.g., 10% mass by volume) can produce a solution with a pH in the above ranges.
  • the second component when hydrated to form a resulting solution of the protein, produces a solution having a pH of greater than or equal to 9, greater than or equal to 9.5, greater than or equal to 10, or greater than or equal to 10.5.
  • the first component and the second component may be dissolved in one or more solvents then combined/mixed together to form a crosslinking hydrogel forming composition comprising a solution of the first component and the second component.
  • the first component is dissolved in a first solvent and the second component is dissolved in a second solvent, which are then combined to form the hydrogel forming composition solution.
  • the hydrogel forming composition solution of the first component and the second component may have a pH that is less than or substantially similar to the pH of the solution of the lyophilized second component.
  • the crosslinking solution of the first component and the second component has a pH greater than or equal to 7, greater than or equal to 8, greater than or equal to 9, greater than or equal to 9.5, greater than or equal to 10, or greater than or equal to 10.5.
  • the crosslinking solution of the first component and the second component has a pH less than or equal to 11, less than or equal to 10.5, less than or equal to 10, or less than or equal to 9.5.
  • the crosslinking solution of the first component and the second component has a pH greater than or equal to 9 and less than or equal to 11
  • the crosslinking solution of the first component and the second component has a pH greater than or equal to 10 and less than or equal to 10.5.
  • Other ranges are also possible.
  • the hydrogel forming composition solution of the first component and the second component is formed by combining an unbuffered solution of the first component with a solution of the second component that has a pH greater than or equal to 10.2 and less than or equal to 10.6.
  • the time it takes for the hydrated hydrogel forming composition to crosslink and form a gel may determine how fast the composition can act as a tissue sealant when the hydrogel/hydrogel forming composition is delivered to a tissue site. It may be beneficial for the hydrogel forming composition to crosslink within a sufficiently short time frame to permit the applied composition to quickly seal a tissue puncture site or other wound surface when the hydrogel forming composition is applied to the tissue site.
  • the “measured gel time” as used herein is determined by dispensing the hydrated first component and the hydrated second component to a vial containing a stir bar on a stir plate adjusted to 300 RPM and recording the initial time (T 0 ) upon dispensing the components of the composition, followed by recording the end time (T F ) when gelation causes the stir bar to stop spinning.
  • the measured crosslink time is the time when the timer is stopped minus the initial time.
  • rheometry may be used to determine the measured gel time.
  • the hydrogel forming composition may have any of a variety of suitable measured gel times for particular uses and application methods.
  • the hydrogel forming composition may have a measured gel time of greater than or equal to 0.1 seconds, greater than or equal to 0.5 seconds, greater than or equal to 1 second, greater than or equal to 2 second, greater than or equal to 3 seconds, greater than or equal to 4 seconds, greater than or equal to 5 seconds, greater than or equal to 10 seconds, or greater than or equal to 15 seconds.
  • the hydrogel forming composition has a measured gel time of less than or equal to 20 seconds, less than or equal to 15 seconds, less than or equal to 10 seconds, less than or equal to 5 seconds, less than or equal to 4 seconds, less than or equal to 3 seconds, less than or equal to 2 seconds, less than or equal to 1 second, or less than or equal to 0.5 seconds. Combinations of the above recited ranges are also possible (e.g., the hydrogel forming composition may have a measured gel time of greater than or equal to 0.1 seconds and less than or equal to 20 seconds, the hydrogel forming composition may have a measured crosslink time of greater than or equal to 1 second and less than or equal to 3 seconds). Other ranges are also possible.
  • the measured gel time may be rendered advantageously short by adjusting the amount of the crosslinking initiator.
  • sufficient crosslinking initiator is added to provide a suitable pH value, as explained herein, to initiate the crosslinking reaction between the crosslinking agent and the protein in a given surgical environment.
  • the crosslinking initiator provides a pH value of greater than or equal to 10 (e.g., between 10.2-10.6, between 10.3-10.4), which facilitates a faster crosslinking reaction since the reaction is generally favored at higher pH values.
  • the gel time is tunable, depending on the amount of the base or basic buffer in the hydrogel forming composition.
  • the hydrogel forming composition may have a sufficiently long measured pot life.
  • measured pot life refers to the duration of time that the hydrated first and second components of the hydrogel forming composition remain usable after hydration of one or more of the powdered reactive components (e.g., the first component and/or the second component) but prior to combining the solutions of the first and second components to form the crosslinking hydrogel forming composition solution.
  • a sufficiently long pot life may advantageously allow the hydrated first and second components of the hydrogel forming composition to remain usable after a user (e.g., a physician) has hydrated the first and second components until the user is ready to deliver the one or more components to the site of administration to form the hydrogel tissue sealant.
  • the “measured pot life” as used herein is determined by measuring certain performance metrics, such as, for example, the gel time and/or the burst strength (both of which are explained herein in greater detail) of a crosslinked hydrogel forming composition or formed hydrogel and comparing to an equivalent hydrogel forming composition or formed hydrogel formed from freshly hydrated first and second components of the hydrogel forming composition that have not been subject to storage or delayed use after hydration.
  • the measured pot life is the time it takes for the performance metric of the crosslinked hydrogel composition resulting from the one or more hydrated components that have been stored for a period of time to differ from the performance metric of the crosslinked hydrogel composition resulting from the one or more freshly hydrated components by a defined percentage (e.g., +/- 10%) based on a clinically based minimum value for each performance metric to ensure that the hydrogel tissue sealant can safely perform its function (e.g., sealing tissue).
  • a defined percentage e.g., +/- 10%
  • the hydrogel forming components of the composition may have any of a variety of suitable pot life times (defined as performance metric differing by no more than +/- 10%).
  • the hydrogel forming composition has a pot life of greater than or equal to 10 minutes, greater than or equal to 20 minutes, greater than or equal to 30 minutes, greater than or equal to 1 hour, greater than or equal to 2 hours, greater than or equal to 5 hours, or greater than or equal to 10 hours.
  • the hydrogel forming composition has a pot life less than or equal to 24 hours, less than or equal to 10 hours, less than or equal to 5 hours, less than or equal to 2 hours, less than or equal to 1 hour, less than or equal to 30 minutes, or less than or equal to 20 minutes.
  • the hydrogel forming composition has a pot life between greater than or equal to 10 minutes and less than or equal to 24 hours, the hydrogel forming composition has a pot life greater than or equal to 1 hour and less than or equal to 2 hours).
  • Other ranges are also possible.
  • the pot life of either or both reagent components of the hydrogel forming composition may be increased, particularly for embodiments where a component is provided in solvated form, by dissolving such component(s) in a biocompatible non-polar organic solvent, such as DMSO, to form the solvated component(s) of the hydrogel forming composition.
  • a biocompatible non-polar organic solvent such as DMSO
  • Use of such a solvent may in certain instances substantially increase the pot life, to be, for example, greater than or equal to 1 week, greater than or equal to 1 month, greater than or equal to 6 months, greater than or equal to 1 year, or greater than or equal to 2 years.
  • the hydrogel forming composition may be advantageous for the hydrogel forming composition to have a sufficiently long measured shelf life.
  • the term “measured shelf life” refers to the duration of time that one or more of the powdered components of the hydrogel forming composition remains suitably usable after storage of the one or more powdered components.
  • a sufficiently long shelf life may advantageously allow the hydrogel forming composition to remain usable after long-term storage of the hydrogel forming composition.
  • the “measured shelf life” as used herein is determined by measuring certain performance metrics, such as, for example, the gel time, dissolution time, and/or the burst strength (which are explained herein in greater detail) of a crosslinking hydrogel forming composition solution and/or a crosslinked hydrogel composition formed therefrom prepared that has been subject to a storage period as compared to the corresponding measured metrics resulting from such one or more powdered components of the hydrogel forming composition (e.g., the first component and/or the second component) that have not been subject to storage prior to hydration.
  • certain performance metrics such as, for example, the gel time, dissolution time, and/or the burst strength (which are explained herein in greater detail) of a crosslinking hydrogel forming composition solution and/or a crosslinked hydrogel composition formed therefrom prepared that has been subject to a storage period as compared to the corresponding measured metrics resulting from such one or more powdered components of the hydrogel forming composition (e.g., the first component and/or the
  • the measured shelf life is the time it takes for the performance metric of the crosslinked hydrogel composition resulting from the one or more powdered components that have been subject to storage for a period of time prior to hydration to differ from the same metric measured for fresh ingredients by a specified percentage (e.g., +/- 10%) based on a clinically based minimum value for each performance metric to ensure that the hydrogel tissue sealant can safely perform its function (e.g., sealing tissue).
  • the first and second components of the hydrogel forming composition may have any of a variety of suitable shelf life times.
  • the hydrogel forming composition has a shelf life (defined as resulting is a difference compared to fresh ingredients of +/- 10%) of greater than or equal to 1 week, greater than or equal to 1 month, greater than or equal to 6 months, greater than or equal to 1 year, greater than or equal to 2 years, greater than or equal to 3 years, or greater than or equal to 4 years.
  • the hydrogel forming composition has a shelf life less than or equal to 5 years, less than or equal to 4 years, less than or equal to 3 years, less than or equal to 2 years, less than or equal to 1 year, less than or equal to 6 months, or less than or equal to 1 month.
  • the hydrogel forming composition has a shelf life between greater than or equal to 1 week and less than or equal to 5 years, the hydrogel forming composition has a shelf life greater than or equal to 1 year and less than or equal to 2 years).
  • Other ranges are also possible.
  • the method comprises forming a crosslinking solution comprising at least a crosslinking agent and a nucleophilic biodegradable polymer (e.g., a protein), wherein forming the crosslinking solution initiates crosslinking of the crosslinking agent and the nucleophilic biodegradable polymer (e.g., a protein), thereby forming the hydrogel tissue sealant.
  • the crosslinking solution comprises a crosslinking initiator, a surfactant, and/or an antioxidant.
  • the method of forming the hydrogel tissue sealant comprises dissolving a first powdered component comprising a crosslinking agent (e.g., an electrophilic biodegradable polymer) and a second powdered component comprising a nucleophilic biodegradable polymer (e.g., a protein) in one or more solvents.
  • a crosslinking agent e.g., an electrophilic biodegradable polymer
  • a second powdered component comprising a nucleophilic biodegradable polymer (e.g., a protein) in one or more solvents.
  • the first component is dissolved in a first solvent (e.g., water or an aqueous solution) and the second component is dissolved in a second solvent (e.g., water or an aqueous solution).
  • the dissolved fist component and the dissolved second component are combined to form a crosslinking hydrogel forming composition in the form of a solution comprising the crosslinking agent and the protein, thereby initiating crosslinking of the crosslinking agent and the nucleophilic biodegradable polymer (e.g., a protein) to from the hydrogel tissue sealant.
  • a crosslinking hydrogel forming composition in the form of a solution comprising the crosslinking agent and the protein, thereby initiating crosslinking of the crosslinking agent and the nucleophilic biodegradable polymer (e.g., a protein) to from the hydrogel tissue sealant.
  • the method of forming a hydrogel tissue sealant comprises hydrating a first powdered component including a crosslinking agent and at least one antioxidant, hydrating a second powdered component including a protein, a crosslinking initiator, and a surfactant, and combining the hydrated first component and the hydrated second component to initiate crosslinking of the crosslinking agent and the protein.
  • FIG. 1 shows steps in such an exemplary method for forming a hydrogel tissue sealant.
  • Method 150 in step 152 comprises hydrating a first powdered component, comprising, for example, a crosslinking agent.
  • the first powdered component optionally comprises an antioxidant.
  • the first powdered component is hydrated with a first solvent comprising water or a first aqueous solution.
  • the first solvent may include, in some embodiments, a radiopaque agent.
  • Step 154 comprises hydrating a second powdered component comprising, for example, a protein.
  • the second powdered component comprises a crosslinking initiator and/or a surfactant.
  • the second powdered component is hydrated with a second solvent comprising water or a second aqueous solution.
  • the second solvent comprises an anti-foaming agent.
  • step 152 and step 154 may occur simultaneously (but in separate containers).
  • Step 156 comprises combining the hydrated first component and the hydrated second component to initiate crosslinking of the crosslinking agent and the protein to form the hydrogel tissue sealant.
  • such a method comprises delivering the hydrogel forming composition comprising the first component and the second component to a tissue site, or delivering a partially or fully crosslinked hydrogel composition to the tissue site, wherein the hydrogel composition comprises the reaction product of the above described first component and second component reagents.
  • the hydrogel composition may be delivered to the tissue site in any of a variety of suitable ways.
  • the first component of the hydrogel forming composition and the second component of the hydrogel forming composition may be at least partially combined to initiate crosslinking prior to delivering the hydrogel composition to the tissue site.
  • the first component of the hydrogel forming composition and the second component of the hydrogel forming composition are fully combined prior to delivering the hydrogel composition to the tissue site.
  • the hydrated first component of the hydrogel forming composition and the hydrated second component of the hydrogel forming composition may crosslink as the hydrogel composition is being delivered to the tissue site.
  • the hydrogel tissue sealant is at least partially formed prior to or upon delivery to the tissue site.
  • the tissue site is a pleural site, such as the parietal pleura and/or the visceral pleura.
  • the hydrogel forming composition may be delivered to the tissue site using one or more syringes, sprayers, or other applicators.
  • the applicator that can be used to deliver the hydrogel forming compositions is described in U.S. Patent Application Serial No. 62/822,490, titled “LUNG BIOPSY FLOWABLE SEALANT DELIVERY SYSTEM,” or PCT /U S 2020/023772 , titled “SEALANT DELIVERY APPARATUS, AND SYSTEM AND METHOD FOR PREPARING SAME, FOR USE IN A LUNG PROCEDURE,” both of which are incorporated herein by reference in their entireties.
  • the hydrogel tissue sealant can be formulated so that it adheres to the tissue site.
  • the adherence of the hydrogel tissue sealant at the tissue site may be determined by a liquid burst pressure strength model based on ASTM F2392-04 (the Standard Test Method for Burst Strength of Surgical Sealants).
  • ASTM F2392-04 the Standard Test Method for Burst Strength of Surgical Sealants
  • the test is designed to determine the pressure needed to rupture the sealant patch covering a simulated liquid leak and indirectly measure the adhesion property of the sealant to simulated tissue.
  • the hydrogel tissue sealant may have any of a variety of suitable burst pressure strengths (e.g., liquid burst pressure strengths).
  • the burst pressure strength of the hydrogel tissue sealant measured by such test is greater than or equal to 10 mm Hg, greater than or equal to 50 mm Hg, greater than or equal to 100 mm Hg, greater than or equal to 150 mm Hg, greater than or equal to 200 mm Hg, or greater than or equal to 250 mm Hg. In certain embodiments, the burst pressure strength of the hydrogel tissue sealant measured by such test is less than or equal to 300 mm Hg, less than or equal to 250 mm Hg, less than or equal to 200 mm Hg, less than or equal to 150 mm Hg, less than or equal to 100 mm Hg, less than or equal to 50 mm Hg.
  • the burst pressure strength of the hydrogel tissue sealant is greater than or equal to 10 mm Hg and less than or equal to 300 mm Hg, the burst pressure strength of the hydrogel tissue sealant is greater than or equal 100 mm Hg and less than or equal to 150 mm Hg).
  • Other ranges are also possible.
  • the crosslinked hydrogel tissue sealant may swell (e.g., with water) after delivery to the tissue site.
  • the hydrogel tissue sealant may have a relatively high swelling rate and/or extent (characterized by mass gain after a defined swelling period).
  • a hydrogel tissue sealant with a relatively high swelling rate may be advantageous, as the hydrogel tissue sealant may swell and conform to the tissue delivery site to improve sealing properties.
  • the hydrogel composition may be delivered to the tissue site via a coaxial cannula.
  • the coaxial cannula becomes surrounded by the hydrogel composition during and/or after delivery of the hydrogel composition in order to perform a biopsy procedure (e.g., a lung biopsy).
  • the coaxial cannula may, in some embodiments, be removed through the bulk of the hydrogel after the biopsy procedure, resulting in a puncture, void, or hole in the hydrogel tissue sealant.
  • the hydrogel tissue sealant may swell (e.g., with water) after removal of the coaxial cannula, therefore substantially closing and/or filling the puncture, void, and/or hole caused by the coaxial cannula.
  • the swelling rate of the hydrogel tissue sealant may be determined by forming the crosslinked hydrogel sealant as explained herein, recording the weight of the hydrogel composition, incubating the hydrogel composition in a phosphate-buffered saline (PBS) solution at 37 °C, removing the hydrogel composition from the PBS solution after two hours, and recording the weight of the hydrogel composition, wherein the percent is calculated by the percent weight gain.
  • PBS phosphate-buffered saline
  • the hydrogel tissue sealant has a swelling mass gain greater than or equal to 30%, greater than or equal to 35%, greater than or equal to 40%, greater than or equal to 45%, greater than or equal to 50%, greater than or equal to 55%, greater than or equal to 60%, or greater than or equal to 65%.
  • the hydrogel tissue sealant has a swelling mass gain less than or equal to 70%, less than or equal to 65%, less than or equal to 60%, less than or equal to 55%, less than or equal to 50%, less than or equal to 45%, less than or equal to 40%, or less than or equal to 35%.
  • the hydrogel tissue sealant has a swelling mass gain between greater than or equal to 30% and less than or equal to 70%, the hydrogel tissue sealant has a swelling rate between greater than or equal to 40% and less than or equal to 50%).
  • Other ranges are also possible.
  • the hydrogel tissue sealant may be utilized as a pleural lung sealant to seal off air and/or fluid from entering the pleural space. In some embodiments, the hydrogel tissue sealant may be utilized to seal the pleura together.
  • the hydrogel tissue sealant may degrade in the subject over time.
  • the degradation time of the hydrogel may be determined by a degradation model based on ASTM F1635 (the Standard Test Method for in Vitro Degradation).
  • ASTM F1635 the Standard Test Method for in Vitro Degradation
  • the test is designed to determine the degradation rate (that is, the mass loss rate) and change in material or structural properties, or both, of materials used in surgical implants.
  • the hydrogel tissue sealant may have any of a variety of suitable degradation times. In some embodiments, for example, the hydrogel tissue sealant has a degradation time greater than or equal to 1 day, greater than or equal to 5 days, greater than or equal to 7 days, greater than or equal to 10 days, or greater than or equal to 15 days.
  • the hydrogel tissue sealant has a degradation time less than or equal to 20 days, less than or equal to 15 days, less than or equal to 10 days, less than or equal to 7 days, or less than or equal to 5 days. Combinations of the above recited ranges are also possible (e.g., the hydrogel tissue sealant has a degradation time between greater than or equal to 1 day and less than or equal to 20 days, the hydrogel tissue sealant has a degradation time between greater than or equal to 10 days and less than or equal to 15 days). Other ranges are also possible.
  • a kit may comprise one or more devices, such as containers or syringes comprising containers (e.g. barrels of the syringes) that are capable of storing one or more components of the hydrogel forming composition, mixing one or more components of the hydrogel forming composition, and/or delivering the hydrogel forming composition (or one or more components thereof) to a tissue site.
  • containers or syringes comprising containers (e.g. barrels of the syringes) that are capable of storing one or more components of the hydrogel forming composition, mixing one or more components of the hydrogel forming composition, and/or delivering the hydrogel forming composition (or one or more components thereof) to a tissue site.
  • FIG. 2A shows, according to certain embodiments, a schematic diagram of a dual- syringe, 4 compartment/container device 200 that is capable of storing and/or mixing one or more components of the hydrogel forming composition with one or more solvents
  • FIG. 3A shows a cross
  • FIG. 2B shows, according to some embodiments, a schematic diagram of a the device of FIG. 2A, where the second syringe component containing the hydrated/dissolved first and second components of the hydrogel forming composition is coupled with a coaxial cannula to be capable of delivering the hydrogel forming composition to a tissue site, and FIG. 3B shows a cross-section thereof.
  • the kit may comprise any of the above described first components contained within a first container, which may, as illustrated in FIGs 2A-3B be conveniently a barrel of a syringe device.
  • syringe device 200 e.g., with two interconnected syringe components of the device configured for mixing the stored components with one or more solvents
  • the first component can comprise the first component comprising the crosslinking agent contained within first barrel/container 102, e.g. during storage.
  • the first component may further comprise an antioxidant (e.g., BHT), a surfactant, and/or a radiopaque agent.
  • the first component may be in the form of a first dry powder.
  • the kit may further comprise a second container containing any of the second components described above.
  • syringe device 200 can contain the second component within second barrel/container 104, e.g. during storage.
  • the second component may include a protein that is capable of crosslinking with the crosslinking agent.
  • the second component may further include a crosslinking initiator that initiates crosslinking of the crosslinking agent with the protein, and/or a surfactant (e.g., PEG 8000).
  • the second component may further comprise a radiopaque agent.
  • the second component may be in the form of a second dry powder.
  • the kit further comprises a third, e.g., solvent, component contained within a third container.
  • the third component comprises a first solvent (e.g., water, DMSO) or solution (e.g., aqueous solution) for dissolving and/or hydrating the first powdered component.
  • the first solvent or solution comprises an antioxidant (e.g., BHT), a radiopaque agent (e.g., KC1), and/or a surfactant.
  • the kit further comprises a fourth, e.g., solvent, component contained within a fourth container.
  • the fourth compartment comprises a second solvent (e.g., water, DMSO) or solution (e.g., aqueous solution) for dissolving and/or hydrating the second powder component.
  • the second solvent or solution comprises a crosslinking initiator (e.g., a base or basic buffer, such as sodium carbonate).
  • the second solvent or solution comprises an antioxidant (e.g., N- acetly-DL-tryptophan), a radiopaque agent, or a surfactant (e.g., Pluronic® L61).
  • first barrel/container 102 and second barrel/container 104 may be double barrels of first a first syringe 100 (e.g., also used in the disclosed embodiment as the applicator syringe — See FIG. 2B), while third barrel/container 106 and fourth barrel/container 108 are double barrels of a second syringe 120 (e.g., containing mixing or hydration solvents).
  • the kit for forming a hydrogel tissue sealant comprises one or more syringes collectively providing at least three separate containers.
  • a kit comprises a first container that contains a first component (e.g., an electrophilic biodegradable polymer) in powder form (e.g., first container 102 in first syringe 100), a second container that contains a second component (e.g., a nucleophilic biodegradable polymer) in powder form (e.g., second container 104 in first syringe 100), and at least a third container that contains one or more solvents (e.g., third container 106 and fourth container 108 in second syringe 120).
  • a first container that contains a first component (e.g., an electrophilic biodegradable polymer) in powder form
  • a second container that contains a second component e.g., a nucleophilic biodegradable polymer
  • a third container that contains one or more solvents (e.g
  • the kit may comprise one or more syringes (e.g., one syringe, two syringes, three syringes, four syringes).
  • the one or more syringes may have any of a variety of suitable configurations.
  • the kit comprises two syringes (e.g., first syringe 100 and second syringe 120).
  • Each syringe of the one or more syringes may, in certain embodiments, be a double-barrel syringe.
  • First syringe 100 may, in some embodiments, comprise first container 102 comprising the first component in powder form and second container 104 comprising the second component in powder form.
  • second syringe 120 e.g., mixing or hydration syringe
  • third container 106 comprising a first solvent able to dissolve the first component
  • fourth container 108 comprising a second solvent able to dissolve the second component.
  • the one or more syringes are configured such that first container 102 and second container 104 are able to be placed in fluid communication with at least third container 106 comprising the one or more solvents.
  • Configuring the kit in this way facilitates the mixing of the first component with the one or more solvents to form a solution of the first component, and facilitates mixing of the second component with the one or more solvents to form a solution of the second component.
  • first syringe 100 e.g., applicator syringe
  • second syringe 120 e.g., mixing or hydration syringe
  • first syringe 100 and second syringe 120 are configured to be fluidically connectable to each other such that first container 102 and second container 104 are able to be placed in separate fluid communication with third container 106 and fourth container 108, respectively, to facilitate mixing of the first component with the first solvent to form a solution of the first component in first container 102, and to facilitate mixing of the second component with the second solvent able to form a solution of the second component in second container 104.
  • the kit may comprise one or more devices that are capable of delivering the hydrogel forming composition (or one or more components thereof) to a tissue site.
  • FIG. 2B shows, according to some embodiments, a schematic diagram of a device that is capable of delivering the hydrogel forming composition to a tissue site
  • FIG. 3B shows a cross-section thereof.
  • device 250 e.g., delivery device
  • the needle assembly comprises coaxial cannula 130 and needle 132, in some embodiments.
  • first syringe 100 is configured to mix and contain the dissolved first component (e.g., the solution of the first component) and the dissolved second component (e.g., the solution of the second component) to form a crosslinking solution of the first component and the second component able to form the hydrogel tissue sealant upon delivery to the tissue site via the needle assembly.
  • the dissolved first component e.g., the solution of the first component
  • the dissolved second component e.g., the solution of the second component
  • FIG. 4 shows, in accordance with certain embodiments, a summary of the steps in an exemplary method for hydrating and delivering a hydrogel forming composition using the device depicted in FIGs. 2A-3B.
  • Method 400 of hydrating and delivering a hydrogel forming composition comprises, in some embodiments, step 402 comprising mechanically and fluidically interconnecting an applicator syringe (e.g., first syringe 100 in FIGs. 2A and 3A) and a mixing syringe (e.g., second syringe 120 in FIGs. 2A and 3A).
  • the applicator syringe e.g., first syringe 100 in FIGs.
  • the mixing syringe (e.g., second syringe 120 in FIGs. 2A and 3A) comprises a third component contained with a third container (e.g., third container 106 in FIGs. 2A and 3A) and a fourth component contained within a fourth container (e.g., fourth container 108 in FIGs. 2A and 3A).
  • method 400 comprises step 404 comprising sequentially depressing the plungers of the applicator syringe (e.g., first syringe 100 in FIGs. 2A and 3A) and the mixing syringe (e.g., second syringe 120 in FIGs. 2A and 3A) to hydrate the first component contained within the first container (e.g., first container 102 in FIGs. 2A and 3A) and the second component contained within the second container (e.g., second container 104 in FIGs. 2A and 3A).
  • Step 406 of method 400 comprises evaluating whether the first component and/or the second component are fully hydrated (e.g., completely dissolved). If the first component and/or the second component are not fully hydrated, then step 404 is repeated. If the first component and the second component are fully hydrated, then the user can proceed to step 408.
  • step 408 of method 400 comprises disconnecting the mixing syringe (e.g., second syringe 120 in FIGs. 2A and 3A) from the applicator syringe (e.g., first syringe 100 in FIGs. 2A and 3A), when the hydrated first component and the hydrated second component are contained in the applicator syringe.
  • Step 410 comprises connecting a needle assembly (e.g., coaxial cannula 130 and needle 132 in FIG. 2B) to the applicator syringe (e.g., first syringe 100 in FIGs. 2B and 3B).
  • a needle assembly e.g., coaxial cannula 130 and needle 132 in FIG. 2B
  • method 400 comprises step 420 comprising deploying the material (e.g., the solution of the first component and the solution of the second component) from the applicator syringe (e.g., first syringe 100 in FIGs. 2B and 3B) to the tissue site.
  • deploying the material comprises mixing the solution of the first component and the solution of the second component to form a crosslinking solution of the first component and the second component as the material is being delivered to the tissue site (e.g., at one or more mixing points within the needle assembly, proximal to the needle assembly and/or at the distal tip of the needle assembly).
  • a needle assembly comprising a coaxial cannula is used to deliver the hydrogel composition and to perform the biopsy procedure (e.g., the lung biopsy).
  • device 250 e.g., delivery device
  • the coaxial cannula into the pleural space of a subject such that the hydrogel forming composition can be deployed at the tissue site.
  • FIG. 8A shows, in accordance with certain embodiments, a schematic diagram of a hydrogel delivery device having a coaxial cannula inserted into the pleural space of a subject. The hydrated hydrogel forming composition is deployed to the tissue site. See, for example, FIG.
  • FIG. 8B which shows, in accordance with certain embodiments, a schematic diagram of the hydrogel delivery device deploying the hydrogel forming composition via the coaxial cannula to provide a hydrogel tissue sealant at the tissue site.
  • the hydrogel forming composition is deployed during, or subsequent to the user advancing the cannula through the tissue site.
  • a biopsy is performed, in some embodiments.
  • syringe component 100 of device 250 is removed from the needle assembly comprising the coaxial cannula, and a biopsy device comprising a standard biopsy needle is inserted through the coaxial cannula.
  • the biopsy e.g., lung biopsy
  • FIG. 8C shows, in accordance with certain embodiments, a schematic diagram of a biopsy needle inserted through the coaxial cannula to perform a biopsy procedure.
  • the biopsy device and the needle assembly comprising the coaxial cannula are removed from the administration site.
  • the hydrogel tissue sealant may swell (e.g., with water), as described herein, sealing any punctures, voids, and/or holes in the hydrogel tissue sealant caused by removal of the needle assembly.
  • one or more of containers/syringes containing one or more of the powdered components may be placed in a sealed pouch (e.g., a sealed foil pouch), optionally flushed with and under an atmosphere of an inert gas such as nitrogen, and further optionally containing a desiccant material within the pouch (e.g., a desiccant or molecular sieve material, such as a desiccant packet containing either PharmaKeep® (Mitsubishi Gas Chemical America, Inc.) or 4A molecular sieves (Multisorb Filtration Group).
  • a sealed pouch e.g., a sealed foil pouch
  • an inert gas such as nitrogen
  • a desiccant material within the pouch e.g., a desiccant or molecular sieve material, such as a desiccant packet containing either PharmaKeep® (Mitsubishi Gas Chemical America, Inc.) or 4A molecular sieves (Multisorb Filtration Group).
  • the following example describes the use of a hydrogel tissue sealant in a swine lung model.
  • a X-ray image of a swine lung model was obtained, as shown in FIG. 5A.
  • FIG. 5B shows the normal airway pressure of a post biopsy image of a swine lung model.
  • the hydrogel forming composition was prepared, comprising the reaction product of PEG(SS) 2 and albumin with iohexol as the radiopaque material.
  • the hydrogel forming composition was delivered upon initial puncture of the lung, via needle (circled), to the swine lung model prior to the biopsy.
  • the hydrogel tissue sealant is visible through the soft tissue and pleural space.
  • the coaxial component of the applicator was left in place, and the sealant application needle was removed.
  • FIG. 6B shows a X-ray image of a swine lung model post biopsy.
  • the hydrogel tissue sealant (circled) is adhered to the parietal pleura of the swine lung model. Furthermore, as shown in FIG. 7B, the hydrogel tissue sealant (circled) is protruding from the inside lung and is adhered to the parietal and visceral pleura of the swine lung model, therefore sealing the biopsy tract.
  • Samples of hydrogel forming compositions including a PEG(SS) 2 -containing component and a recombinant human serum albumin (rHS A) -containing component were generated according to Table 1.
  • PEG(SS) 2 was obtained from Sigma (Samples 1, 3, and 4) or Laysan Bio (Sample 2) and handled under a nitrogen environment.
  • the PEG(SS) 2 -containing component comprised either PEG(SS) 2 or PEG(SS) 2 with added BHT.
  • a desiccant or molecular sieve material was also enclosed in the pouch — the desiccant packet containing either PharmaKeep® (Mitsubishi Gas Chemical America, Inc.) or 4 A molecular sieves (Multisorb Filtration Group).
  • the PEG(SS) 2 - containing component was aliquoted into a first syringe and stored in a sealed foil pouch under an atmosphere of nitrogen gas.
  • the rHSA-containing component solution used to prepare, via lyophilization, the rHSA-containing component used for forming the hydrogel included rHSA obtained from InVitria (Junction City, KS), with added sodium carbonate, and PEG 8000, combined with reverse osmosis (RO) water so that the concentration of the rHSA was 30% mass by volume.
  • the rHSA-containing component solution in the RO water was lyophilized, ground into a powder, aliquoted into a second syringe, and sealed in a foil pouch under a nitrogen environment.
  • a hydration kit was created using deionized (DI) water in a third syringe (for hydrating the PEG(SS) 2 -containing component) and DI water containing Pluronic® L61 in a fourth syringe (for hydrating the lyophilized rHSA-containing component).
  • DI deionized
  • the hydration kit was sealed in a foil pouch with two Leur-Lock® connectors to be connected to each syringe so that the powders mixtures could be hydrated at the point of use.
  • the samples received two doses of electron beam sterilization. All samples were stored and conditioned at 40° C to simulate advanced aging compared to room- temperature storage.
  • Table 1 Components of tested hydrogel forming compositions.
  • the samples were aged according to Table 2, pulled at the indicated time point, and evaluated, as explained in further detail below.
  • Table 2 Stability time points for the hydrogel forming composition and the corresponding simulated advanced age.
  • the gel times of the four hydrogel forming composition samples denoted in Table 1 were evaluated at each stability time point by: (i) hydrating the PEG(SS) 2 - containing component and the rHSA-containing component, (ii) waiting for a period of two minutes, thirty minutes, or sixty minutes after hydration, (iii) dispensing the hydrated components into a vial containing a stir bar on a stir plate adjusted to 300 RPM, (iv) recording the initial time upon dispensing the components, and (v) recording the end time when gelation caused the stir bar to stop spinning. Results are shown in Table 3.
  • the dissolution times of the four rHSA-containing component samples denoted in Table 1 were evaluated at each stability time point by: (i) connecting the syringe containing the rHSA-containing component with the syringe containing DI water and Pluronic® L61, (ii) starting a timer, (iii) pushing the fluid back and forth into the powder syringe, and (iv) stopping the timer when the rHSA-containing component completely dissolved. Results are shown in Table 4.
  • Table 4 Dissolution times of rHSA-containing components for samples aged for the indicated Stability Time Point (average of three replicate measurements).
  • the pHs of the four rHSA-containing component samples denoted in Table 1 were evaluated at each stability time point by: (i) dissolving the powder mixture with the syringe containing the DI water and Pluronic® L61 as described above for the dissolution time measurement, and (ii) measuring the pH of the solution using a calibrated Mettler Toledo FiveEasy pH Meter. Results are shown in Table 5.
  • the swelling rates of the hydrogel compositions formed from the four samples denoted in Table 1 were evaluated at each stability time point by: (i) forming the hydrogel composition by hydrating the PEG(SS) 2 -containing component and the rHSA- containing component, dispensing the components through a mixing tip, and allowing them to gel; (ii) recording the weight of the hydrogel composition at time zero, (iii) incubating the hydrogel composition in a phosphate-buffered saline (PBS) solution at 37 °C, (iv) removing the hydrogel composition from the PBS solution after two hours; and (v) recording the weight of the hydrogel composition. The percent swelling was calculated by percentage weight gain. Results are shown in Table 6.
  • Table 6 Swelling rates of tested hydrogel compositions at two hours for samples agec for the indicated Stability Time Point (average of three replicate measurements).
  • Hydrogel compositions including PEG(SS) 2 and rHSA were generated according to Table 7.
  • the rHSA-containing component included rHSA lyophilized with Pluronic® L61 and an antioxidant. Forty-five samples of three different hydrogel forming compositions were investigated. The percent mass by volume of rHSA varied from 10- 30% between compositions, and the amount of PEG(SS) 2 also varied so that the NHS ester : amine ratio was kept constant for all three compositions at 2.21.
  • Table 7 Components of tested hydrogel forming compositions.
  • the powdered PEG(SS) 2 and the rHSA-containing component were aliquoted into their own syringe and each was hydrated with a separate syringe containing 1 mL of water. The components were then dispensed through a mixing tip and allowed to gel. The adherence of the hydrogel composition was determined by a liquid burst pressure model based on ASTM F2392-04 (the Standard Test Method for Surgical Sealants). Results are shown in Table 8.
  • Table 8 Average liquid burst pressure strength of tested hydrogel compositions (average of forty-five replicate measurements).
  • inventive hydrogel compositions as a sealant for use during lung biopsy procedures in swine models to prevent pneumothorax complications.
  • the rHSA-containing component solution used to prepare, via lyophilization, the rHSA-containing component used for forming the hydrogel included rHSA with added sodium carbonate, PEG 8000, and Pluronic® L61, combined with RO water.
  • the rHSA-containing component solution in the RO water was lyophilized, ground into a powder, aliquoted into a second syringe, and sealed in a foil pouch under a nitrogen environment.
  • a hydration kit (e.g., a double barrel syringe) was created using DI water in a first compartment of the double barrel syringe (for hydrating the PEG(SS) 2 -containing component) and DI water in a second compartment of the double barrel syringe (for hydrating the lyophilized rHSA-containing component).
  • the hydration kit was sealed in a foil pouch with connections to each syringe containing PEG(SS) 2 and the rHSA- containing component so that the powder mixtures could be hydrated with their respective solution at the point of use.
  • a total of ten swine subjects were evaluated. Five of the ten swine were designated as test subjects and were implanted with a hydrogel composition in the left lower lung lobe.
  • a coaxial technique was utilized with computed tomography (CT) guidance.
  • CT computed tomography
  • the delivery device was inserted through the soft tissue until adjacent to the lung and pleural space (see FIG. 8A).
  • the hydrogel composition was hydrated and deployed through the ported needle system of the delivery device into the subcutaneous tissue, pleural space, and the immediately adjacent area of the lung parenchyma (see FIG. 8B).
  • CT imaging was used to confirm placement of the hydrogel.
  • a lung biopsy was taken through use of a coaxial cannula within five minutes of implantation of the hydrogel composition. Briefly, the needle was adjusted as needed and advanced to the site of the biopsy and the ported needle delivery system was removed. A standard biopsy needle was inserted through the coaxial system, and a standard lung biopsy procedure was performed continuing to use CT guidance, utilizing 16G Bard Mission Biopsy Needles (see FIG. 8C).
  • a follow-up evaluation for two of the five test subjects was performed at 72 ( ⁇ 8) hours post-implantation of the hydrogel, and evaluation of the other three swine was performed at 144 ( ⁇ 8) hours post-implantation.
  • a CT scan was completed to assess for the presence of the hydrogel composition and the presence (or absence) of pneumothorax. After completing the CT scan, the animals were euthanized and a comprehensive necropsy was performed with target organs (i.e., the lung) removed for gross pathologic observation. The inner chest wall (e.g., the parietal pleura) was also examined.
  • the five control swine received lung biopsy procedures as described above but without implantation of the hydrogel composition.
  • Follow-up evaluations including a CT scan to assess for the presence (or absence) of pneumothorax) were performed at 48 ( ⁇ 8) hours post-lung biopsy. The animals were then euthanized after their CT scan (unless otherwise noted) and a comprehensive necropsy was performed with target organs removed for gross pathologic observation.
  • Table 9 Summary of swine model study design.
  • hydrogel compositions in the day 6 test subjects demonstrated a decrease in hydrogel firmness, indicating resorption. All five test subjects showed minor irritation on the parietal pleura surrounding the needle insertion site, but nothing warranting major concern.
  • the five control subjects received a lung biopsy without application of the hydrogel composition.
  • Two of the five control subjects i.e., Subjects 9 and 10) developed intraprocedural pneumothorax and a subsequent air embolism, as revealed by CT.
  • FIG. 9B shows an example of an air embolism (circled) for Subject 9
  • FIG. 9C shows an example of pneumothorax (circled) for Subject 10. Due to the severe nature of these complications, the two test subjects were terminated after completing the biopsy.
  • the three remaining control subjects tolerated the lung biopsy, and CT scans at the time of follow up showed one swine with a large pneumothorax present (i.e., Subject 6, see FIG. 9D, wherein the circles indicate pneumothorax).
  • the other two swine i.e., Subjects 7 and 8) were clear and free of complications. Necropsy revealed nothing of note for any of the control subjects.
  • Table 10 Summary of test results for the evaluation of pneumothorax in test and control subjects. While several embodiments of the present invention have been described and illustrated herein, those of ordinary skill in the art will readily envision a variety of other means and/or structures for performing the functions and/or obtaining the results and/or one or more of the advantages described herein, and each of such variations and/or modifications is deemed to be within the scope of the present invention. More generally, those skilled in the art will readily appreciate that all parameters, dimensions, materials, and configurations described herein are meant to be exemplary and that the actual parameters, dimensions, materials, and/or configurations will depend upon the specific application or applications for which the teachings of the present invention is/are used.
  • a reference to “A and/or B,” when used in conjunction with open-ended language such as “comprising” can refer, in one embodiment, to A without B (optionally including elements other than B); in another embodiment, to B without A (optionally including elements other than A); in yet another embodiment, to both A and B (optionally including other elements); etc.
  • At least one of A and B can refer, in one embodiment, to at least one, optionally including more than one, A, with no B present (and optionally including elements other than B); in another embodiment, to at least one, optionally including more than one, B, with no A present (and optionally including elements other than A); in yet another embodiment, to at least one, optionally including more than one, A, and at least one, optionally including more than one, B (and optionally including other elements); etc.
EP21719341.6A 2020-03-20 2021-03-19 Reactive hydrogel forming formulations and related methods Pending EP4121131A1 (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US202062992881P 2020-03-20 2020-03-20
PCT/US2021/023359 WO2021189024A1 (en) 2020-03-20 2021-03-19 Reactive hydrogel forming formulations and related methods

Publications (1)

Publication Number Publication Date
EP4121131A1 true EP4121131A1 (en) 2023-01-25

Family

ID=75539929

Family Applications (1)

Application Number Title Priority Date Filing Date
EP21719341.6A Pending EP4121131A1 (en) 2020-03-20 2021-03-19 Reactive hydrogel forming formulations and related methods

Country Status (6)

Country Link
EP (1) EP4121131A1 (zh)
JP (1) JP2023518290A (zh)
CN (1) CN115515653A (zh)
AU (1) AU2021237731A1 (zh)
CA (1) CA3175344A1 (zh)
WO (1) WO2021189024A1 (zh)

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11739166B2 (en) 2020-07-02 2023-08-29 Davol Inc. Reactive polysaccharide-based hemostatic agent

Family Cites Families (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
IL47468A (en) 1975-06-12 1979-05-31 Rehovot Res Prod Process for the cross-linking of proteins using water soluble cross-linking agents
US4839345A (en) 1985-03-09 1989-06-13 Nippon Oil And Fats Co., Ltd. Hydrated adhesive gel and method for preparing the same
US5583114A (en) 1994-07-27 1996-12-10 Minnesota Mining And Manufacturing Company Adhesive sealant composition
USRE38827E1 (en) 1994-07-27 2005-10-11 3M Innovative Properties Company Adhesive sealant composition
US6458095B1 (en) * 1997-10-22 2002-10-01 3M Innovative Properties Company Dispenser for an adhesive tissue sealant having a housing with multiple cavities
US20020022588A1 (en) * 1998-06-23 2002-02-21 James Wilkie Methods and compositions for sealing tissue leaks
US6458147B1 (en) 1998-11-06 2002-10-01 Neomend, Inc. Compositions, systems, and methods for arresting or controlling bleeding or fluid leakage in body tissue
CA2398668C (en) 2000-02-17 2010-06-15 3M Innovative Properties Company Delivery systems using preformed biodegradable polymer compositions and methods
TWI436793B (zh) * 2006-08-02 2014-05-11 Baxter Int 快速作用之乾密封膠及其使用和製造方法
US9002133B2 (en) 2013-02-27 2015-04-07 Sharp Laboratories Of America, Inc. Multi layered image enhancement technique

Also Published As

Publication number Publication date
WO2021189024A9 (en) 2022-10-06
CA3175344A1 (en) 2021-09-23
CN115515653A (zh) 2022-12-23
AU2021237731A1 (en) 2022-09-29
WO2021189024A1 (en) 2021-09-23
JP2023518290A (ja) 2023-04-28

Similar Documents

Publication Publication Date Title
AU2014236385B2 (en) Biocompatible hydrogel polymer matrix for delivery of cells
RU2453340C2 (ru) Полимерный тканевый герметик
JP2011078764A (ja) 外科手術用組成物
JP2018149414A (ja) 癒着防止材
AU2019396194A1 (en) Compositions and methods for treating wounds
AU2021237731A1 (en) Reactive hydrogel forming formulations and related methods
US20230094351A1 (en) Reactive hydrogel forming formulations and related methods, including methods of preparation
CN117618628A (zh) 可生物降解的肺密封剂

Legal Events

Date Code Title Description
STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: UNKNOWN

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE INTERNATIONAL PUBLICATION HAS BEEN MADE

PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: REQUEST FOR EXAMINATION WAS MADE

17P Request for examination filed

Effective date: 20220928

AK Designated contracting states

Kind code of ref document: A1

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

DAV Request for validation of the european patent (deleted)
DAX Request for extension of the european patent (deleted)