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Publication numberUS3322125 A
Publication typeGrant
Publication dateMay 30, 1967
Filing dateApr 4, 1966
Priority dateApr 4, 1966
Also published asDE1642080A1, DE1642080B2, DE1792785A1, DE1792785B1, DE1792785C2
Publication numberUS 3322125 A, US 3322125A, US-A-3322125, US3322125 A, US3322125A
InventorsLeonard D Kurtz
Original AssigneeSutures Inc
Export CitationBiBTeX, EndNote, RefMan
External Links: USPTO, USPTO Assignment, Espacenet
Sutures and method of making same
US 3322125 A
Abstract  available in
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Claims  available in
Description  (OCR text may contain errors)

United States Patent 3,322,125 SUTURES AND METHOD OF MAKING SAME Leonard D. Kurtz, Woodmere, N.Y., assignor to Sutures lnc., Coventry, Conn. No Drawing. Filed Apr. 4, 1966, Ser. No. 539,619 4 Claims. (Cl. 128-3355) This application is a continuation in part of application Ser. No. 230,284 filed Oct. 12, 1962, now abandoned.

This invention relates to surgical sutures. More particularly, the invention relates to polyfilamentous sutures having decreased reactivity with tissue.

Sutures are classified either as absorbable or nonabsorbable and may be polyfilamentous or monofilamentous. Polyfilament sutures are preferred by surgeons because they have superior knotting characteristics relative to monofilament materials. On the other hand, monofilament sutures are preferable for the patient as there is less trouble in cases of infection.

It is generally accepted that monofilaments, such as monofilament stainless steel, monofilament nylon, monofilament polyethylene and monofilament polypropylene are the most inert of the non-absorbable sutures. When implanted in areas where infection occurs, as a rule, they are not spit spontaneously by the wound, nor do they require surgical removal. On cross-section, all of these monofilaments have one thing in common. They are solid with no dead spaces or interstices.

On the other hand, all braided and all twisted sutures when implanted where infection occurs, will, as a rule, be spit spontaneously by the wound or require surgical removal in order for healing to occur. All of these braided and twisted materials have one thing in common. On cross-section, they consist of many filaments and dead spaces. For example, on cross-section, braided silk has 40 to 50 percent dead space.

On the basis of the above facts, it seems possible that there is a direct relationship between dead spaces in a suture and the incidence of spontaneous spitting or the necessity for'surgical removal of the suture when infection occurs. If this hypothesis is correct, monofilam ents should be the sutures of choice for the patient undergoing surgery. However, surgeons have a great deal of difliculty in their use. All of them are stiff, difiicult to knot, and have a tendency to open spontaneously. Some, in addition, have sharp ends, kink or are too elastic. All monofilaments apparently pose difliculties in surgical techniques. Many surgeons continue to use these despite the problems because of the excellent patient response. However, obviously, monofilaments cannot be used if the surgical knotting technique becomes inadequate.

It is an object of the present invention to provide a method whereby polyfilament sutures can be imbued with monofilament properties. It is a further object to provide polyfilament sutures having attributes of a monofilament suture.

These and other objects which will become apparent in light of the description which includes a preferred embodiment are achieved according to the invention by substantially eliminating the dead air spaces in a polyfilamentous suture by substantially filling the interstices of a polyfilament suture with a plurality of particles of an inert material. It has been discovered that the reactivity of the polyfilament suture can be reduced to such an extent that reactivity of the suture is as low as reactivity of a monofilament when these solid particles are incorporated therein.

The sutures which can be improved according to this invention include all non-absorbable sutures. However, for reasons appearing hereinafter, polyfilament sutures made from materials which do not swell in water such as "ice the hydrophobic synthetics, polyesters, polyolefins, polyamides and the like are more suited to improvement by the present invention than those made from materials like silk which do swell in water.

The inert material used to fill the sutures may be particles of an inert material which are small enough to penetrate the interstices of the suture. Teflon (polytetrafluoroethylene) particles are particularly suitable asare particles of the other inert and insoluble synthetic resins such as those mentioned which can be used as sutures. Aqueous dispersions of these materials, such as the aqueous dispersions of Teflon described in Berry, US. Patent No. 2,478,229 are suitable to incorporate the particles into the suture. Saturated aqueous dispersions are particularly suitable.

Sutures made in accordance with the invention have been tried in hundreds of clinical cases and the results have been very successful. In the smaller sutures (sizes 30 and below) substantially all clinical results with the sutures tested were as good as with a monofilament suture. With larger sutures, results are improved with respect to untreated sutures but have not been as free from reaction within the suture as with monofilaments.

It is believed that by substantially filling the dead space within the interstices of the suture, the pockets which are conducive to harboring invading organisms are eliminated or at least reduced to an extent that the clinical results indicate that the suture is monofilamentous. In other words, while it is not certain that the voids are eliminated, the sutures produced in accordance with this invention behave clinically like a monofilament. The exact amount of particles necessary to fill the dead spaces within the suture varies with the nature and configuration of the suture and, of course, on the density of the particulate matter. In general, however, with hydrophobic sutures which do not swell in water such as polyesters etc., a minimum of about 5 percent by weight up to as much as may be crammed into the suture and which will remain there can be used to render the suture substantially monofilamentous. The maximum will depend on techniques as well as materials and pressurized impregnations may be used. It should be noted, however, that substantial elimination of tissue reaction can be achieved without filling the suture to an extent equal to a theoretical maximum. For example, clinical results show that with from about 8 to 14 percent by weight of Teflon particles, a polyester suture can be rendered substantially non-reactive. The theoretical amount of Teflon which could be incorporated, however, is substantially higher. Since silk and the like swell in use, however, it is preferred to modify hydrophobic type sutures according to the invention.

Wax, of course, has been used for treating polyfilament silk sutures for years. Other materials, such as silicones, have also been proposed to treat polyfilament sutures for various reasons. In these and all analogous instances, however, the sutures when used clinically have behaved like polyfilaments and not like monofilaments. It is believed that this result is due primarily to the use of dispersions of particles to load the suture with particulate matter. The old wax-type treatments have been strictly concerned with the use of solutions of the wax material.

Example I A 4-0 suture made from Du Pont type 55 Dacron is immersed in a suspension of colloidal size Teflon particles available from Du Pont as Teflon TE3170, and having an average particle size of about 0.2 micron. The suspension described by Berry, US. Patent No. 2,478,229 is also suitable for this purpose. The suture has a four thread core of 56 denier and a braided cover made with a twelve carrier braider with two threads of 13-15 denier per carrier. Total denier of this conventional suture was 392. The polymer of the Dacron fiber is polyethylene terephthalate, a polyester wherein the ester linkage occurs in the polymer chain. The impregnation was continued for several minutes and water was removed and the suture dried. The weight gain was about 9 percent. The suture was then hot stretched at a platen temperature of 450 F. on a six-spindle hot stretching machine made by the W. M. Steel Company (model 115), 40 percent based on its original length.

The suture before treatment was naturally water proof and thus non-capillary. In clinical use the untreated suture caused a normal amount of tissue reaction. Clinical use of the treated suture, however, was essentially free of any reaction and the suture behaved as a monofilament. Hundreds of other sutures ranging in size from 30 to 6-0 were used and, of these, all but those of sizes above 30 behaved substantially like monofilaments. Some incidences of tissue reaction were reported with clinical use of the larger sutures but much less reaction occurred than would be normal with these sutures. In preparing these sutures, the length and nature of the impregnation treatment was such that from about 8 to 14 percent of Teflon particles by weight based on the polyester suture were incorporated into the suture. The particles of Teflon remain tenaciously imbedded in the body of the suture and repeated wash cycles will not dislodge a detectable amount thereof. The combination of Teflon and polyester type sutures is particularly advantageous because the suture is rendered softer and thus more knottable as is fully described in my co-pending application Ser. No. 220,085, filed Aug. 28, 1962, now abandoned. The amount of Teflon necessary to render sutures non-reactive according to the present invention is higher than that necessary to impart improved knottability to the suture, but incorporation of such higher amounts within the interstices of the suture does not destroy the beneficial effect of incorporating lesser amounts therein. Teflon is thus preferred with other polyestersutures such as those made from the linear condensation products of terephthalic acids and fdiols such as Kodel and Tereylene.

.or 30 percent by weight of the particles may be incorporated into the suture. Of course the suture may be loosely braided in which case more particles may be necessary. In general, however, conventional sutures will be sufiiciently loaded with the stated amount.

Hot stretching by ordinary means is employed with hot.

stretchable polyfilamentous sutures to reduce the elasticity thereof as is customary with such materials. This procedure has the effect of reducing the diameter of the suture which is generally desirable but even more so in this case because the dead spaces are probably reduced even further.

The sutures can be sterilized in the usual manner and at any stage of manufacture or may be sterilized by the user. Sutures which tend to swell in water or steam may be sterilized by electromagnetic radiation techniques or ethylene oxide. The sutures may, of course, be attached to surgical needles which can either be'eyed or eyeless.

I claim:

1.- A method imparting attributes of a monofilament to a polyfilament suture comprising the steps of immersing a hydrophobic polyfilamentary polyester suture in an aqueous dispersion of solid polytetrafluoroethylene particles, the particles being of a size sufl'lciently small to enter Within the interstices of the polyfilament suture, maintaining the immersion to impregnate the suture with the polytetrafluoroethylene particles to substantially fill the dead spaces of the polyfilament suture, drying the suture to remove the fluid carrier to provide a polyfilament suture having the dead spaces therein filled by said particles of polytetrafluoroethylene.

v 2. A method according to claim 1, wherein the suture is polyethylene terephthalate and the particles of polytetrafluoroethylene have an average size of not more than 1 micron.

3. A method according to claim 1, wherein the suture is polyethylene terephthalate and is filled with from. 8 to 14 percent by weight of polytetrafluoroethylene particles based on the weight of said suture.

4. A suture comprising a polyfilamentary strand of polyethylene terephthalate having a plurality of fine solid particles of polytetrafiuoroethylene incorporated in the interstices thereof to an extent sufiicient to substantially fill the dead air spaces to imbue the polyfilament suture with the properties of a monofilament.

References Cited UNITED STATES PATENTS 2,478,229 8/1949 Berry 260-23 X 2,576,576 11/1951 Cresswell et al. 117-1395 X 2,590,586 3/1952 Thompson et al 117-161 2,734,506 2/1956 Nichols et al 128'335.5 2,823,576 2/1958 Needham et al. 1l77 2,825,706 3/1958 Sanders 117-138.8 2,870,045 1/1959 Corkum 117-161 X 2,930,106 3/1960 Wrotnowski et al. 117161 3,113,369 12/1963 Barrett et al 117139.5 X 3,187,752 6/1965 Glick 128-335,

WILLIAM D. MARTIN, Primary Examiner, T. G. DAVIS, Assistant Exqminer,

Patent Citations
Cited PatentFiling datePublication dateApplicantTitle
US2478229 *Sep 5, 1946Aug 9, 1949Du PontConcentrated aqueous colloidal dispersions of polytetrafluoroethylene and methods for their preparation
US2576576 *Apr 19, 1946Nov 27, 1951American Cyanamid CoLubricated thread
US2590586 *Nov 21, 1951Mar 25, 1952Heminway & Bartlett Mfg CoFish net formed of synthetic resin strands and strands therefor and method of producing same
US2734506 *Dec 14, 1953Feb 14, 1956 Silk sutures and ligatures
US2823576 *Mar 2, 1953Feb 18, 1958Drummondville Cotton Company LMethod of making slip-free fish netting
US2825706 *Nov 23, 1954Mar 4, 1958Du PontCoating compositions comprising polytetrafluoroethylene and phenol aldehyde, and article coated therewith
US2870045 *Dec 17, 1956Jan 20, 1959American Thread CoImpregnated synthetic fiber sewing thread and method of making same
US2930106 *Mar 14, 1957Mar 29, 1960American Felt CompanyGaskets
US3113369 *May 2, 1960Dec 10, 1963Monsanto ChemicalsYarn manufacture and products obtained thereby
US3187752 *Apr 27, 1962Jun 8, 1965American Cyanamid CoNon-absorbable silicone coated sutures and method of making
Referenced by
Citing PatentFiling datePublication dateApplicantTitle
US3390681 *Apr 4, 1966Jul 2, 1968Sutures IncPolyester suture having improved knotting characteristics
US3527650 *Dec 21, 1967Sep 8, 1970Ethicon IncSuture coating of polyethylene or polytetrafluoroethylene
US3665927 *May 29, 1968May 30, 1972Sutures IncImpregnation of polyfilamentous sutures with synthetic polymer particles
US3867190 *Apr 24, 1973Feb 18, 1975American Cyanamid CoReducing capillarity of polyglycolic acid sutures
US4105034 *Jun 10, 1977Aug 8, 1978Ethicon, Inc.Poly(alkylene oxalate) absorbable coating for sutures
US4461298 *Jul 26, 1982Jul 24, 1984Ethicon, Inc.Composite sutures of silk and hydrophobic thermoplastic elastomers
US4470941 *Jun 2, 1982Sep 11, 1984Bioresearch Inc.Preparation of composite surgical sutures
US5222978 *Aug 16, 1990Jun 29, 1993United States Surgical CorporationPackaged synthetic absorbable surgical elements
US5312642 *Mar 5, 1993May 17, 1994United States Surgical CorporationMethod and apparatus for calendering and coating/filling sutures
US5359831 *Jun 18, 1993Nov 1, 1994United States Surgical CorporationMolded suture retainer
US5366081 *Jul 10, 1992Nov 22, 1994United States Surgical CorporationPackaged synthetic absorbable surgical elements
US5447100 *Feb 14, 1994Sep 5, 1995United States Surgical CorporationApparatus for calendering sutures in orthogonal directions
US5468252 *Jun 22, 1993Nov 21, 1995United States Surgical CorporationPackaged synthetic absorbable surgical elements
US5534288 *Feb 16, 1995Jul 9, 1996United States Surgical CorporationInfection-resistant surgical devices and methods of making them
US5540773 *May 18, 1995Jul 30, 1996United States Surgical CorporationApparatus for calendering and coating/filling sutures
US5584875 *Apr 13, 1994Dec 17, 1996C. R. Bard, Inc.Method for making vascular grafts
US6203564Feb 26, 1998Mar 20, 2001United States SurgicalBraided polyester suture and implantable medical device
Classifications
U.S. Classification606/230, 427/430.1, 606/231, 427/2.31
International ClassificationA61L17/14
Cooperative ClassificationA61L17/145
European ClassificationA61L17/14C