CA2108734C - Polyurethane pressure-sensitive adhesives - Google Patents

Abstract

Pressure-sensitive adhesives which possess absorptivity and/or permeability properties to remove transepidermal wager loss and/or other bodily fluids that come into contact with the adhesive, in combination with a fine balance of cohesion and adhesion properties, can be formulated by controlling the crosslinking of a polyurethane polymer having excess hydroxyl functionality, a glass transition temperature of less than about 0°C, a moisture absorption of at least about 20% of its weight and/or a moisture vapor transmission rate of at least about 300 grams/meter2/24 hours measured at 37°C and a 90%
relative humidity gradient. Adhesives of these polymers possess a peel adhesion to human skin of between about 0.3 and 4 newtons/cm width of the polymer or adhesive.

Description

POLYURETHANE PRESSURE-SENSITIVE ADHESIVES
This invention relates to polyurethane pressure-sensitive adhes>ives. More particularly, this invention relates to polyurethane pressure-sensitive adhesives which exhibit a high degree of water absorption and~'or high water vapor transmission capabilities so as to be especially suitable for use in a medical article for application to human skin.
Another aspect of this invention relates to medical devices, including o;stomy devices and wound dressings, which incorporate such polyurethane pressure-sensitive adhesives therein.
Until the early 1950's, commonly used pressure-sensitive adhescives ("PSAs") for skin applications were based on natural or synthetic rubber compositions compounded with low molecular weight tackifiers, plasticizers, ~;tabil:izers, etc. These adhesives had the disadvantage of being quite hydrophobic and incapable of absorbing water. Thus, such adhesives would trap water undcer the covered area, often causing skin maceration or other skin damage. Furthermore, the low molecu).ar weight ingredients compounded into these adhesives> often would penetrate the s~;in, causing irritation or sensitization.
Polyacrylate PSAs are an improvement over the rubber-based adhesives, partly due to their self-adhesive property. 'this property allows them to be prepared as single-component polymeric materia~.s without the need for potentially allergenic modifying or tackifying agents. However, these adhesives often contain unreact:ed residual acrylic monomer as an impurity in an amount which would irritate and/or x'10873 4 sensitize skin.. Although these polyacrylate PSJ~s are much more permcaable to moisture or water vapor than are the rubber--based adhesives, they are incapahle of absorbing any significant amounts of moisture or water. Therefore, when used for long duration in skin or wound care applications, adhesion is compromised and/or skin damage o:r maceration may result.
One variat=ion of these polyacrylate PSns ~s disclosed in U..S. Patent 4,914,173 to Ansell. The specific PSAs of that patent are obtained by reacting an isocyanate prepal:ymer, which is the reaction product of a poly-functional isocyanate and a polyoxyalkylensa diol monoalkyl ether, with a hydroxy-containing estE~r of .acrylic or methacrylic acid to form a functionalized prepolymer and then cross-linking the polymer :by irradiation to form a >?SA that is not self-adherent but is capable of absorbing up to 95% by weight of water when hydrated. Although useful in application:a where the adhesive will contact: a moist or wet environment, these adhesives do nut have sufficient tack or initial adhesive properties to be adherent to them skin for certain uses.
An advance in P,SA formulation for skin and particularly for wound care applications was the development of compositions comprising blends c~f one or more water-:~olubl~e or swellable hydrocolloids and a tacky, viscous,, polymeric material such as polyisobut-ylens~ as disclosed in Chen U.S. Patent No.

3,339,546. Another example is Doyle et al. U.S.
Patent No. 4,551,490 which discloses medicinal grade pressure-sensii=ive compositions containing polyisbbutylens:s or blends of polyisobutylenes and butyl rubber, <3 styrenic radical or b) ock type copolymer, minE~ral oil and water soluble l~ydrocolloid gum and a tack.i.fier. Such Uydrocolloid cont<-rio~nc~
PSAs have the advantage of providing the desired '10 ~ ,7 3 4 adhesion to skin and, at the same time, are capable of absorbing trar~sepidEarmal Water loss (i.e., perspiration) or other body fluids, including wound exudates.
Hydrocolloid containing PSAs have found use in medical applications such as ostomy devices and wound dressings, where thEa adhesives maintain the device on skin for several days without skin damage. Ilowever, existing hydre~collo~.d PSAs have certain limitations in that they are opaque, lack quick initial tack, and tend to disintegrate upon excessive water absorption.
Polyurethanes are polymeric products of diols or polyols and diisocyanates or polyisocyanates. Despite the broad applications of polyurethane chemistry, polyurethane based PSAs are not widely used and to date have been found suitable for only a few specialized applications. A suitable balance of elastic and viscous properties which is required in a PSA has not been readily attainable in conventional polyurethane materials.
Existing polyurethane based adhesives function either as weak elastics or simply as high viscosity liquids. The adhesives composed of the elastic type polyurethanes tend t:o fail by gradually peeling away from surfaces to which they have been applied. The high viscosity type polyurethanes, which are typically obtained by using a substantial excess of polyol, leave a residue upon removal, and their cohesive strength is too low to withstand the stresses applied in many applications.
The difficulty of attaining this balance of viscoelastic characteristics in a polyurethane explains the paucity of prior art polyurethane PSA
literature. hllen et al. U.S. Patent No. 4,497,914 discloses an ostomy gasket adhesive comprised of a polyurethane prepared by reaction of an organic 1 ~1~~';3 ~
polyisocyanate with one or more di or polyfunctional hydroxyl compounds, for example, polyols derived from propylene or s~thylene oxide, in which is incorporated a hydrophilic filler, such as a cellulosic or natural gum. The adhE~sive is capable of absorbing bodily fluids by vi.rt:ue of dispersed hydrophilic filler physically enc:apsul;ated within the self-sustaining polyurethane ~~dhesive composition.
Muller et: al. ~:J. S. Patent No. 3, 930, 102 discloses the preparation of ~~ webstock having a self-adhesive polyurethane coating produced by the reaction of a trifunctional propylene oxide based polyol and an aliphatic dii:aocyan;ate employing an NCO/OH ratio in the range of 0.71 to 0.85. This type of webstock is said to be suitable for the production of labels and tapes. Howevsar, the=_se compositions are not sufficiently hydrophilic to allow absorption of bodily fluids .
A need thus exists for polyurethane pressure-sensitive adhs~sives for skin application which have adequate moisture aJbsorption or permeation capacities and have other- desi:red properties, such as transparency, confo:rmability to body shape, quick tack, adhesivs~ strength tailorable to the application, high wet strength, .and lack of cold flow.
This invention relates to pressure-sensitive adhesives comprising a polyurethane polymer having excess hydrox;rl functionality, a glass transition temperature o1: less than about 0°C, a moisture absorption at equilibrium of at least about 20% of its weight and/or a moisture vapor transmission rate of at least about 300 gr~ms/meter'/24 hours measured at 37°C
and a 90% rel<~tive humidity gradient. Advantageously, the glass transition temperature of the polymer is _ CV0006 ~11~8~' 3 4 less than aboui~ -30°C, the moisture absorption at equilibrium of at least about 100% of its weight and/or the moi:~ture 'vapor transmission rate is at least about 500 grams/meter2/24 hours. These polymers provide a peel adhesion to human skin of between about 0.3 and 4 and preferably between about 0.5 and 3.5 newtons/cm wid~;.h of the polymer.
Preferabl!~, the polyurethane polymer is formed by the reaction o;E an isocyanate component and a polyol 1o component at a molar ratio of isocyanate moieties to hydroxyl moieties of less than one with at least one of the components having a functionality that is greater than t~ao to facilitate crosslinking. The polymer is cro:~slinked to a crosslink density alpha (a) defined by the equation ~ XI (Fi-2) (1.05-r) Mw wherein i = 1 to n where n is the number of the reactant components Xi = mole fraction of i''' component Fi = functionality of the i'~ component r = 'the NCO/OH molar ratio Mw = :Molecular weight of the polyol of between about 10~' and 10' to obtain the desired properties. When the isocyanate component is an aliphatic polyisocyanate, the crosslink density is " 6 - CV0006 ~1 ~08~3 4 preferably be~:ween about 2 x 10'' and 10'3, while for aromatic poly:isocyanates the crosslink density is preferably bei~ween about 4 x l0'' and 9 x l0''.
A preferred molar ratio is between about 0.5 and 0.99, and mores preferably between about 0.65 and 0.9.
The polyol component advantageously comprises a polyether polyol having a molecular weight of between about 1000 and 10,000, such as a homopolymer or copolymer containing ethylene oxide or propylene oxide groups. The polyol component may also be a hydroxyl terminated prEpolymer. When moisture absorbent adhesives are desired, the polyol component can be a polyether dio7_ or t:riol containing at least about 30%
by weight of Ethylene oxide groups.
The isoc~~anate component has a functionality of equal to or greater than 2, and may be an aliphatic polyisocyanatE, an aromatic polyisocyanate or combinations t:hereo:f. Also, the isocyanate component may be an isoc:yanate terminated prepolymer.. 11s noted, at least one of the isocyanate or polyol components must have a functionality of greater than 2 to obtain the desired crosslinking of the polymer.
The invention also relates to a medical article or device for application to skin which comprises a layer of the ~>ressure-sensitive adhesive described above and a backing material in contact with at least a portion of c>ne side of the layer. The backing material may x>e a natural or synthetic fiber, a woven or non-woven fabric, paper or a thermoplastic polymer.
Also, a releaece layer in contact with the side of the pressure-sensitive adhesive layer opposite the backing material may be included to protect the adhesive prior to use. Thus, the release layer comprises a material that does not permanently bond to the pressure-sensitive adhesive layer, such as a silicone coating.

~108~'3 4 This medical article may also include a backing layer and a layer of the pressure-sensitive adhesive described above on at least a portion of one side of the backing layer for contacting the skin and securing the article thereto. This article advantageously includes a moisture or water absorbent material positioned for placement upon a moist or wet environment, wherein the pressure-sensitive adhesive layer is located adjacent at least a portion of the absorbent material. If the absorbent material is in the form of a disk, the pressure-sensitive material layer may be associated with and at least partially surround the perimeter of the disk. A support layer may be provided for the absorbent material, such that the pressure-sensitive adhesive layer is attached onto at least a portion of the periphery of the support layer and surrounds the entire perimeter of the disk.
In another embodiment, the medical article further comprises an attachment member for connection to another medical f~evice, such as a bag or container.
Thus, the disk woulf~. include an aperture therein to permit passage of a fluid therethrough. To provide a secure attachment to the patient and to prevent leakage, means for joining the pressure-sensitive adhesive layer to the support layer may be used, such as an ultrasonic weld.
Accordingly, the medical article or device of the invention may be provided in the form of an ostomy device, a wound dre~,sing, a medical tape, a bandage, 3o an incontinence device, a dermatological device, a transdermal device, a surgical incise drape or an intravenous catheter securement device.
Another embodiment of the invention relates to a method for making a pressure-sensitive adtiesi.ve for application to skin which comprises providing a mixture of an isocyanate component and a polyol component at a molar- ratio of isocyanate moieties to hydroxyl moieties of less than one; selecting at least one of the component, to have a functionality that is greater than two to facilitate crosslinking; and reacting the isocyanate and polyol components in the presence of a catalyst to form a polyurethane polymer having a glass transaition temperature of less than about 0°C, a moisture absorption at equilibrium of at least about 20% of i.ts weight and/or a vapor transmission rate of at least about 300 grams/meter2/24 hours measured at 3~~°C and a 90% relative humidity gradient.
The mixture may be cast upon a substrate and heated at a sufficie=nt temperature of between about 100 and 150°C and for a sufficient time of between about 1 to 25 minuteas to form a layer of the polymer.
This layer may be provided upon a backing material or a release layer and would possess a peel adhesion to human skin of betweEan about 0.3 and 4 and preferably between about 0.5 and 3.5 newtons/cm width of the polymer.
Fig. 1 is a graph showing the effect of the a value on peel strength of pressure-sensitive polyurethane adhesives made from aliphatic diisocyanates.
Fig. 2 is a graph showing the effect of the a value on peel strength of pressure-sensitive polyurethane adhesives made from aromatic diisocyanates.
Fig. 3 is a graph showing the correlation between peel strength of pre=ssure-sensitive polyurethane adhesives in vitro versus peel strength in vivo.
Fig. 4 is a front view of an ostomy gasket which includes a PSA band in accordance with the invention.
Fig. 5 is a rear view of the gasket of fig. 4.

_ g _ Fig. 6 is an enlarged cross-sectional view of the gasket of Figs. 4 and 5.
The invention provides polyurethane pressure-sensitive adhesive compositions and medical articles or devices incorporating such adhesives. These adhesives are particularly useful in applications requiring contact with the skin. They thus may be used as adhesives for ostomy care and incontinence appliances, bandages, drug delivery systems, and other devices which are intended to be attached to the skin.
It has been discovered that polyurethane pressure=sensitive adhesives suitable for medical use should possess two distinct characteristics. one characteristic is their absorptivity and/or permeability to remove from the application site transepidermal water loss and/or other bodily fluids that come into contact with the adhesive. The other characteristic is a fine balance of cohesion and adhesion of the polyurethane. It was also discovered that this balance of cohesion and adhesion can be obtained by controlling the crosslinking of the polymer within well defined limits.
The polyurethane is prepared by reacting a polyol having a molecular weight of from about 1,000 to about 10,000 or mixtures of such polyols, With an isocyanate such as a polyisocyanate. Although any of a wide variety of polyols can be used, those which are not 3o crystalline are the most suitable. Exemplary polyols include polyether diols or triols (ethylene oxide and propylene oxide polymers and copolymers) such as those available from Olin (e.g., the Poly GTM series). In general, for comparable formulations, the higher molecular weight polyols would provide greater peel strengths in the resulting adhesive.

1~ _ Where increased moisture or water abs~rpt.i.on properties are desired in the PSA, polyols that contain a significant amount of polyoxyettiylene are used so as to increase the hydrophilic character of the polymer. These polyols should contain at least about 30% of polyoxyethylene in order to enable the polymer to absorb water in an amount of at least about 20% of its weight and as high as 400 to 1000%.
Typical polyols which are useful for this embodiment include Dow Chemical's XUS151.7G and the various commercial Carbowaxes which are available in a range of molecular weights from the Union carbide Corporation. Representative Carbowaxes are PEG
(CarbowaxTM 1450) and PEG (CarbowaxTM 8000) i.n which the numbers refer to molecular weights. The E.»oportion of polyoxyethylene which is present in the polyol will determine the degree of hydrophilic character of the polyurethane. Increasing the amount of polyoxyethylene promotes strong hydrophilic: properties 2o to the final product, while a lessened l~ydropl~ilic character results by increasing the proportio« of 'polyoxypropylene in the polyol.
The functionality of the polyol that is used is at least 2 and usually is greater than 2, with the higher functionalities providing increased crosslinking of the polyurethane. A number of suitable polyols are listed in Table 1 below.
The isocyanates which may be used in making the polYurethanes of the PSAs of the invention may be represented by R(NCO! wherein n is at least 2 and preferably between about 2 and 4, and R is an aliphatic, alicyclic, aliphatic--alicyclic, aromatic, or aliphatic-aromatic hydrc~c:arbon compound ranging from about 4 to 26 carbon atoms, but more conventionally from about 6 to ~0 and generally from about 6 to 13 carbon atoms.

TA : SUITABLE POLYP
COMPONENT: FUNCTIONALITY EQUIVALENT T0 SUT'PLIER
1.

POLY GT"' 55-28 2 2025.00 3t) OLIN

55-37 2 1512.00 3t) OLIN

55-56 2 976.00 45 OLIN

76-120 3 457.00 30 OLIN

83-34 3 15'76.00 70 OLIN

85-28 3 2025.00 10 OLIN

85-36 3 1508.00 17 OLIN

vox~roL"' S 14 8 3 2 3 57 . 19 DOW

5287 2 1018.00 12 DOW

54?1 3 1603.00 14 DOW

vosar~" 220-037 2 1500.00 t) DOW ' 232-034 3 1636.00 1.A DUW

240-446 4.5 125.10 0 DOW

240-800 4 69.70 U DOW

270-370 7 155.90 t) DOW

xusTM 1517 6 . 00 2 1500 . 00 3 t) OOW

ricnx~NOL'~ 3400 3 1000.00 t) MORAY

tHtn.Tx~rloLT" 3 3 19 9 7 . t? MORAY

MULTRANOLT'a 9133 3 53.95 0 MORAY

DESMOgENT~' 2500 2 505.00 t) MORAY

QUADROLT"' 4 73.00 t) MO>3AY

1450 2 714.00 10a CARHIOE

3350 2 1638.Q0 1U() CnRHIDE

4600 2 2352.00 ,1.0t)CARBIDE

8000 2 4141.00 100 CARBIDE

TERATHANST~ 1000 2 . 500 t) DLIPONT
, 2000 2 1024.00 t) 1)UPONT

PLUR.ACOLT"~ 380 3 2235.00 t) BASF

POLY THFT~ ER 1250 2 625 t) 1311SF

FOMREZTM EPD-56 2 1041. 00 4 5 WITCO

EPD-28 2 20$6.00 45 IaITCO

K22-1?0 6 308.00 9l) WITCO

L49-28 3 1990.00 7!i V11'I'CO

ECFL10007 3 278.00 ~a t~ITCO

WITCONL PEG1000L 2 505.00 ~t~ l~.tTCO

_ 12 -TABLE 2: SUITABLE ISOCYANA7.'ES
FUNCTION' COMPONENT: ALITY EQUIVALENT SUPPLIER

p~ITM g4 2 .2 131. 50 ~ UOW' p~~TM 2580 3 139.60 UOW

ISONATETM 2181 2 182.60 1)0W

ISONATET" 2125M~ 2 125.50 1)0W

2 7 131. 0 0 M OBAY

MONDURT"' MR

2 14 3 . 00 MOBAY

MONDURT"' nD 3 323.00 MORAY

MONDURTM Cs75 2 132.00 D90HAY

DESMODURT'' 2 122.10 CYANAMID
w TMXDI 3 404.00 CYANhMID

CyTHANETM 316 2 $ 7 . 0 0 OLI N

TDI so 2 295.77 IIBNKEL

Representative examples of dii.soc:y:w,~tc~s include aliphatic isocyanates such as tet~rnmeti~ylene diisocyanate; hexamethylene diisocyanate;
- trimethylhexamethylene diisocyanate; dimcr .7c..ic3 diisocyanate; isophorone diisocyanate; d.ietliylt~~nzene diisocyanate; decamethylene 1, 1.0-diisocynn~t:o;
cyclohexylene 1, 2-d.i .i.socyanate and cylohex~~ I enc:-1, 4-diisocyanate and the aromatic isocyanate~: ~;ucl~ as 2, 4-and 2,6-tolylene dii~ocyanate; 4,4-di~~heny.lmethane diisocyanate; 1,4-natohthalene diisocyanatc;
dianisidine diisocyar~ate; toluidine diis~c~wr~ate;
m-xylylene diisocyanate; tetrahydronaphtltal ene-1, 5-diisocyanate; and bis(4-isaryanatophenyl)mctl~ane.
Polymeric polyisocyanates having a functionality of greater than 2, such as nc~opeotyl tetraisocyanate, can also be used. I~ numl~~,r° 01' suitable .isocyanates are listed in Table 2 below. rn addition, mixtures of di- and tri-functic~nul isocyanates are commercially available and may be used 2o to obtain an isocyanate components havir~c~ a functionality of between 2 and 3, while mi~:turc~s of tri- and tetra-functional isocyanates ma~~ I~c wed to obtain functionalities of between 3 and a (i..e., DESMODURTM N 3300 from Miles, Perkasie, PA). These tri-and tetra-functional. isocyanates are illustrated below.
r~o l ccrr2~
r~
'' o_c / ~. c_o (cH2~6'"~/~CH 'l6 3 5 t~Ctr~ r>co NL~O t7t~U
(C~i2) 6 (CIA; )6 o-c''r ~ c-o o-c~ ~c-o l I I I
N NI N N
~Ctt2)6 ~~C~ ~ \)i ~C~)b~Q~ ~CII2)6 NOON HC~)N
DesmodurTM N 3300 has a functionality of about 3.4-3.6 and it is a mixture of the two isocyanates depicted above. This isocyanate compound is preferred from the standpoint of toxicity because it is an aliphatic isocyanate derivative that produces a non-toxic degradation product. Furthermore, the isocyanate compounds shown above can be mixed together or with the diisocyanates mentioned above to attain the desired functionality of the isocyanate component.
Generally speaking, the polyurethane is prepared from about 75% to 95% of the polyol, and about 5% to 25% of the polyi.socyanate. The relative amounts are selected so that the NCO/OI~ ratio is between about 0.5 and 0.99 and preferably between about 0..65 to 0.9, so that these polyurethanes have excess hydroxyl functionality.
Tn preparing the polyether polyurethane adhesives of this invention, the polyols and the .
polyisocyanates are reacted in the presence of known catalysts for such reaction, for example, tin salts and organic tin esters such as dibutyltin dilaurate and stannous octoate. ,A,n advantageous catalyst is METACURETM T-12 by Air Products and Chemical , Inc., because this catalyst has been approved by the FDA for medical applications and provides satisfactory reaction.
The adhesive is prepared by first casting a mixture of the isocyanates, polyols, and catalyst onto the desired substrate and curing it by heating at about 100-150°C for about 1-25 and preferably about 3-10 minutes. It is. also possible to initially form an isocyanate terminated prepolymer from a portion of the polyol and the i.socyanate, and then to react that l0 prepolymer with the balance of the polyo.l.. 1s noted above, there is a greater equivalent weight of. polyol compared to isocyanate, such that the final. polymer is, in effect, a pol.yol terminated polyurethane polymer.
Also, it is preferred for the pressure-sensitive adhesive t:o have a glass transition temperature (Tg) of less than 0°C and preferably less than -30°C. Thus, t:he amount of crystalline polyol used, if any, should be held to a minimum. By 2o choosing polypis whi..ch are not crystalline or do not crystallize, or which do not cause phase separation during reaction, a transparent, uncolored polymer is obtained. A c.olorecl polymer is also avoided by selecting isocyanatc: and polyol components wlp eh form polymerization products that do not contai.ro multiple bonds which would be capable of absorbing light or heat energy arid undergo transformations re::ulting in colors.
The pressure-sensitive polyurethane adhesives of this invention each have an MVTR (at equilibrium) of at least 3Ci0 and preferably greater than 500 g/m2/day when measured at 37°C and a 90% r~1_ative humidity gradient. When these adhesives are applied onto skin, the skin can "breathe", such that any excess moisture generated by perspiration of tale skin can pass through thn adhesive to prevent deterioration of the skin, while some moisture is retained to provide an environment which promotes healing.
For applications where the PSAs encounter a highly moist or wet environment, the PSA can be formulated to absorb more than 20% of water based on the weight of the adhesive in addition to providing the desired MVTR. These adhesives are formulated with polyols that contain a significant amount of polyoxvethvlene so as to increase the hydrophilic character of the polymer. The CarbowaxTM polyols mentioned, above are available with as high as 70~ by weight of polyoxyethylene and can be used to provide the desired water absorption properties of the polymer. These water absorptive adhesives contain all of the required properties of the PSAs previously described.
Another feature of the pressure-sensitive adhesives of the present invention is that the amount of leachables is relatively low. Gel chromatography studies show that unreacted polyols are the only components in the extracted media. In addition, the amount of leachables can be controlled by the molar ratio of the components used to form the polymer, the degree of crosslinking of the polymer and tZie chemistry of the polyol components.
A quantitative measure of the pressure-sensitive adhesive characteristics of a material is its peel strength to a desired substrate. nlthough the desired substrate for a medical adhesive is living human skin, peel adhesion is more conveniently measured on a standard substrate, namely a stainless V
steel test panel for quality control purposes. These test values can be correlated to those which are desired for adhesion to human shin. ns noted above, peel strength to human skin for polyurethane adhesives for medical uses range from about 0.3 to 4 newtons/cm.

- 17 - ~.V0006 width of the adhesive, depending upon the backing and the stresses t:he adhesive is expected to encounter during its use, and preferably between about 0.5 and 3.5 newtons/cm. width for adhesion to human skin.
It has been discovered that the polyurethane adhesive peel strength, for a given backing and at a given adhesive thic~;ness, is a function of the extent of crosslinking which, in turn, depends upon the functionality of the components used to form the polyurethane polymer. The extent of crosslinking can be expressed as the number of crosslinks per unit weight. With a greater extent of crosslinking, the peel adhesion becomea lower, such that peel adhesion has been found to be: inversely related to the extent of crosslinking.
It has furttoer been found that this crosslink density is a function of an interplay of molecular parameters of the polyurethane components. A
mathematical relationship incorporating these components has been derived to define the optimum combination of the kind and proportions of the components which results in the formation of polyurethane PSAs for the specified medical uses.
This relationship can be used to calculate a value, designated as a, which is representative of. tt~e extent of crosslinking of t:he polymer. Thus, the a value, which is based on tine average functiona)ity of the reactants, the NCO/OH mole ratio, and the molecular weight of the polyol, may be used as a measure of the performance of one polymer relative to another, as well as to select which polymers are useful i.n accordance with the teachings of the present invention.
The following expression sets forth tl~e relationship between the variables which >> used to calculate a. As noted above, the peel ~tnength is ~11~8~ 3 ~
inversely proportional to the extent of crosslinking, which can be expres:;ed as follows:
Desired Peel Strength =
K
number of crosslinks/unit weight of polymer wherein the number of crosslinks/unit weight of polymer is proportional to a as calculated by the following forrr'ula:wherein ~ XI (Fi-2) ~, N n (1.05-r) Mw i = 1 to n where n is the number of the reactant components Xi. = mole fraction of i°' component Fi. = functionality of the i"' component r = the NCO/OH molar ratio Mw = Molecular weight of the polyo)..
Thus, in a given polyurethane formulation, an interplay of different parameters governs the peel strength of the adhesive. Interdependence of these parameters, and its conformance to the above equation was demonstrated by plotting the a value for a large number of polyurethane adhesive formulations against their peel strength, as shown in Figures 1 ana 2. The supporting data for these figures are set forth in Tables 3 and ~~ .

j ~~ ~ ~ 19 CV0006 An a value in the range of 10'' to 10'' i s representative of an adhesive which has the desired balance of cohesive and adhesive characteristics which are typically required for a pressure-sensitive adhesive, with a values of between 2 x 10-'' and 10-~ for aliphatic pols~urethanes and between 4 and 9 x 10~° for aromatic polyurethanes being particularly advantageous.
Accordingly, based upon this information, one l0 skilled in them art can routinely select the particular isocyanate and polyol components and molar ratios thereof to obi:ain polyurethane polymers which have a values which i:all i:n the desired ranges. In addition, the a value can be ~~alculated prior to actual formulation o1' the ;polymer, so that the experimental work is necessary only after selecting those components and molar ratios which provide a values in the desired range.
Thus, one skilled in the art can tailor the peel strength to a apecific application by the selection of polymers having a particular a value.
For example, a wound dressing generally requires a PSA
that has the <:apability of absorbing a relatively large amount of fluid but a relatively lower degree of peel strength., In comparison, when a medical device is to be attached t~o the patient by these PShs, a relatively higher degree of peel strength is a sually necessary. One can determine mathematically whether any specific combination of components used to form a polymer would have the desired properties and, if not, how to modify the polymer to either increase or decrease the cx value to achieve the desired result.

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Polyurethane Formulations Based on Aliphatic Isooyanatea POLY DESMODURTM DESMODURTM
GTM-55-37 N-3300 8 Peel Water Polyol PolyisocyanateDiisocyanateNCO/OH StrengthDptake (wt%) Cwt%) (wt%) Ratio (N/em) (%) 92.387 5.464 2.150 0.88 0.278 112.8238 92.200 5.808 1.992 0.88 0.280 107.9190 92.292 5.458 2.250 0.90 0.314 117.?052 92.106 5.802 2.092 0.90 0.331 108.7643 92.578 5.832 1.590 0.80 0.400 137.7215 92.483 5.826 1.691 0.82 0.426 132.7077 92.481 5.469 2.050 0.86 0.491 114.4501 .

92.294 5.814 1.892 0.86 0.496 116.5878 92.671 5.480 1.849 0.82 0.514 142.0639 92.669 5.123 2.208 0.86 0.564 126.2756 92.767 5.486 (.747 0.80 0.589 140.8154 92.388 5.820 1.792 0.84 0.595 126.4657 92.576 5.475 1.949 0.84 0.596 123.5098 92.794 4.533 2.673 0.90 O.G29 95.4500 92.771 5.842 1.387 0.76 0.643 159.5735 92.676 5.836 1.487 0.78 O.G7G 155.8120 92.860 5.133 2.007 0.82 0.682 150.7584 92.889 , 4.538 2.573 0.88 0.708 119.9588 92.765 5.128 2.107 0.84 0.723 149.9817 92.866 5.848 1.286 0.74 0.750 197.1354 92.920 4.300 2.780 0.90 0.755 .123.6279 92.667 4.765 2.567 0.90 0.757 126.4355 93.054 5.144 1.803 0.78 0.7(i1 172.0021 92.985 4.542 2.472 0.86 0.767 154.2247 92.958 5.496 1.545 0.76 0.787 176.4395 92.479 5.112 2.408 0.90 0.799 118.0265 93.016 4.304 2.684 0.88 O.R01 122.3668 92.858 4.775 2.367 0.86 0.805 132.7454 92.956 5.139 1.906 0.80 0.805 172.8320 92.863 5.491 1.646 0.78 0.827 180.9655 92.594 5.118 2.308 0.88 U.85U 127.8587 93.081 4.547 2.372 0.84 0.853 201.9966 93.112 4.309 2.579 0.86 0.886 148.8468 93.177 4.552 2.27 0.82 U.89U 236.1296 92.763 4.770 2.467 0.88 0.925 137.7454 93.149 5.149 1.702 0.76 0.967 225.9732 POLY DfiSMODURT""DBSMODUFtTM
GT"'-55-37 N-3300 H Peel iVat~r Polyol PolyisocyanateDiisocyanateNCO/OH Strength Uptake (wt%) iwt%) (wt%) Ratio (N/em) (%) 93.208 4.313 2.478 0.84 0.976 1?2.7290 93.047 4.066 2.88'7 0.90 0.986 129.7297 93.054 5.502 1.445 0.74 0.987 210.3826 93.244 4.793 1.963 0.78 1.021 187.2292 93.244 5.154 1.601 0.?4 1.03 242.3910 93.305 4.318 2.378 0.82 1.050 192.0912 93.143 4.070 2.786 0.88 1.080 143.0732 93.336 4.079 2.5 85 0.84 1.131 168.0455 93.050 4.785 2.16S 0.82 1.173 192.9631 93.436 4.785 1.779 0.74 1.409 294.2116 93.239 4.075 2.686 0.86 1.444 209.99?8 93.146 4.790 2.064 0.80 1.582 255.5226 93.371 4.561 2.068 0.78 1.740 241.6005 93.433 4.083 2.484 0.82 1.744 223.8497 92.954 4.780 2.2Gf~ 0.84 1.880 161.5703 93.499 4.327 2.17a 0.78 1.891 310:0115 93.529 4.08? 2.383 0.80 2.001 242.7349 93.401 4.322 2.277 0.80 2.083 243.5749 93.273 4.556 2.170 0.80 2.252 274.8556 93.626 4.091 2.282. 0.?8 2.659 258.3830 The pressure-sensitive adhesive products of this invention are prepared by coating a mixture of the polyurethane adhesive components on a backing material and allowing the polyurethane components to cure. Useful backing materials are thermoplastic elastomers such as polyurethane film, plasticized PVC, breathable woven or non-woven fabrics made of natural or synthetic fibers such as polyester and porous paper. The adhesive: components can also be applied to l0 a release liner such as mylar film with a silicone coating and silicone: coated paper and then after curing removed and placed on a backing material. The thickness of the adhesive coating is about 1 to 60 mils depending upon the requirements of the specific product application, while the backing material has a thickness in the range of between about 0.5 and 5 mils and typically about 1-2 mils.
The above-described polyurethane pressure-sensitive adhesives are particularly useful for attaching medical devices and other materials to the skin. The adhesives, can be used as or applied to bandages, ostomy devices, incontinence devices, incise drapes, intravenous catheter holders, transdermal drug delivery devices ands medical tapes such as wound closure tapes. Where absorbent adhesives are desired, such as in wound dressings, the polymers that have high water absorption properties can be successfully used. Because of the skin adhesion properties of these PSAs, i.e., no skin irritation or sensitization, and lack of skin or hair adhesion on removal, these adhesives are skin friendly and are very useful in the medical field where skin contact is required.
Figures 4-6 illustrate an ostomy gasket 10 which includes adhe~;ives made of the polymers of the present invention. This device has a central aperture 15 for placement over the incision and through which fluids may drain. Adjacent to and surrounding the aperture 15 is a layer 20 of an adhesive material which has highly absorbent properties to withstand the moist environment and fluids which drain through the aperture. This layer 20 is preferably made of material such as STOMAHESIVETM, which is available from ConvaTech, Skillman, New Jersey. Alternatively, this layer 20 of absorbent material can be of a pressure-sensitive adhesive in accordance with the invention which includes a high ethylene oxide content. Also, other highly absorbent materials, even ones that,do not have adhesive properties, can be used for this component, since the primary function of this layer 20 is to be able to withstand and absorb water or body fluids.
This absorbent material 20 is preferably supported on a polyethylene film 25. When an adhesive material such as STOMAHESIVETM or the like is used, the opposite side (or working face) of this layer 20 includes release liner 30 which allows handling of the article without concern as to the absorbent material adhering to unintended surfaces.
The polyethylene film support 25 is secured to a flange 35 which is adapted to receive an ostomy bottle or other container for storing the fluid which passes through aperture 15. Thus, flange 35 includes a lip ~0 and corresponding recess 45 to facilitate attachment of the bottle or container thereto. Flange is attached to disk shaped extension 50. A
30 supportive adhesive band 55 in accordance with the invention completely surrounds the periphery of the flange 35. This band 55 includes a polyester fiber backing layer 60 upon which is placed an adhesive such as that of Example 9 of the present application. This 35 adhesive is shown as 65. To prevent the adhesive from sticking to surfaces prior to the desired time of ~~se, 210~87~4 - 27 - ;V0006 a release layer 70 :is provided on the side opposite the backing layer (:i.e., the adhesive face). As shown in Fig. 5, the backing layer includes cut notches 75 to facilitate removing a portion of the backing 80 and thus more easily expose the adhesive face for attachment to the dEasired surfaces.
Adhesive band 55 is attached to the top of flange extension 50 and adhered thereto due to the adhesive properties of layer 65. To obtain a more l0 secure connection bsatween band 55 and flange portion 50, a plastic ring 85 is placed upon the backing member 60 of t:he band 55 and is ultrasonically welded to extension 50 of flange 35.
When t:he device is to be used, the release layers 70 and 30 are first removed thus exposing the PSA material E.5 of band 55 and the absorbent material 20. The PSA material 65 as noted above is skin friendly and provides a secure bond to the skin without damaging it.. Thus, the gasket is retained in the desired place despite whether absorbent layer 20 has adhesive c:haraci=eristics or not. When absorbent layer 20 is made of a highly water absorbent material, it most often does not develop sufficient tack or green strength so that it can be properly secured in place on the patieni~. Thus, the PSA adhesive 65 provides a secure bonding of the gasket to the patient and holds the absorbent layer in place so that any further bonding due to the adhesive properties of absorbent 20 c:an occur over time. Again, as noted above, PSA layer 65 allows the skin to breathe so that excessive fluid doer not accumulate thereon and cause damage or other detrimental affects to the skin.
The following examples, which are intended to illustrate the' invention described herein without unduly restricting .it, provide further illustrations of how to selE~ct the appropriate components and - 28 - _ amounts thereof to form the desired pressure-sensitive adhesives.
EXAMPLES
In order to understand the formulations and properties of the adhesives Which are described in these examples, the following abbreviations and test protocols are used.
ABBREVIATIONS:
DESMODURT"' H: Hexamethylene diisocyanate (Miles, Inc., Perkasie, PA).

DESMODURTM A polymeric aliphatic isocyanate N 3300:

based on hexamethylene diisocyanate with an NCO content of 21.6% (Miles) DESMODURTM W: An aliphatic diisocyanate; i.e., dicyclohexylmethane-4,4'-diisacyanate (Miles) DEG: Diethylene glycol (a chain extender).

ISON 2181: Polymeric MDI Functionality 2 (Dow Chemical Company, Midland, MI).

MEDIFILMT"' MF428: An elastic polyurethane film (Bertek: St. Albans, CT).

METACURETM T12: Dibutyl tin dilaurate (Air Products:

Allentown, PA).

A diphenylmethane diisocyanate (MDI) PAPITM 94:

containing methylene bisphenyl isocyanate and polymethylene polyphenyl isocyanate (Dow Chemical Company) PAPITM 2580: A polymethylene polyphenylisocyanate that contains methylene diisocyanate (MDI) having an NCO content of 30.8%

(Dow Chemical Company).

POLY GTM-26-37: A polyether diol of a hydroxyl terminated poly (oxyalkylene) polyol (Olin Corporation, Stamford, CT) POLY GTM-55-28: An eth lene oxide ca y pped diol having a nominal molecular weight of 4,000 with 85% ethylene oxide end groups (Olin Corporation).

POLY GTM-55-37: A difunctional random copolyol containing 35% ethylene oxide and 75%

1o propylene oxide, with 85% ethylene axide end groups (Olin Corporation).

POLY GTM-55-56: An ethylene oxide capped diol having a nominal molecular weight of 2,000 with 87% ethylene oxide end groups (Olin Corporation).

POLY GTM-83-34: ~, glycerol-based triol having a nominal molecular weight of 4,500 which is a hereto polyether polyol with a high ethylene oxide content (Olin Corporation).

XUSTM15176: Copolymer of 30% ethylene oxide and 70% propylene oxide, molecular weight 3000 and a functionality of 2 (Dow Chemical Company).

BALL TACK TEST
Samples are tested according to the Rolling Ball Tack Test method of PSTC-6 in "Test Methods for Pressure-Sensitive Tapes" published by the Pressur.e-Sensitive Tape Council. A Standard Incline Ramp as specified by PSTC-6 with stainless steel balls was used.'-The ramp is placed aver the pressure-sensitive adhesive sample and the distance from the end of the ramp to the middle point of the sample is measured after releasing the ball down the ramp.

- 30 - .T _ CV0006 WATER UPTAKE (WU) TEST
The protocol for this test is set forth as follows:
1. Cut 1/2" disk of material (sample).

2. Weight aluminum weighing dish (W1).

3. Weigh samples (W2).

4. Remove backing from sample and weigh (W3 ) .

5. Place sample with adhesive side up into dish and fill dish with water to submerge sample.

6. Soak sample for 24 hours.

7. Remove sample from dish, shake off excess water and weigh sample.

Water Uptake = W4 - (W2 - W3) x 100 PEEL TEST
2o Samplers are tested according to the Stainless Steel Plate Peel 180° Test of PSTC-1 in the "Test Methods for Pr~sssure-Sensitive Tapes" published by the Pressure-Sensitive Tape Council. A 1" wide by 4"
length strip of sample is applied to a stainless steel Plate. A rolling pin is passed back and forth over the sample once and the plate is secured in an Instron Material Tester and the strip peeled at 180° at a speed of 200 m:m/min. The force is recorded.
As noted above, the peel adhesion of the polyurethane adhesive on human skin is not the same as that on the stainless steel panel, but the former property varies linearly with the latter property, as shown in Figure 3. Thus, one can conduct peel tests on stainless steel sheets and correlate the results to what is necessary for actual skin adhesion values.

WATER VAPOR TRANSMISSION TEST
ASTM Standard Test Methods of Water Vapor Transmission e~f MatEarials Designation: E96-80 was used. The Water Method paragraph 3.2 of the test method was used.
In the Water Method, a dish is prepared containing distilled water and weighings are made to determine the rate of vapor movement through the specimen from the water to a controlled atmosphere.
TEST METHOD FOR PEEL ADHESIONSFROM HUMAN SKIN
Apparatus U~~ed: Instron Material Tester with a load cell capable of accommodating the specified range of force.
Sample: Healthy, clean skin free of creams or lotions.
Sample Preparation: Cut 1" x 3" strips of sample from each material to be tested. Remove the Silicone Release Paper (SRP) and apply adhesive side to the inner forearm. The strips are placed in a row down the width of the arm.
Procedure: Samples are removed at appropriate time intervals. The' lower 1/2" end of the sample strip is loosened and affixed to the upper grips with a strip of 1" masking tape. The forearm is placed under the upper grips and the sample strip is removed at a speed of 200 mm/min. The resulting force is recorded and the subject's skin is assessed for any irritation or adhesive residue.
EXAMPLE 1: Adhesives were made from a polyisocyanate having-a functional~~ty of 2.8 and a mixture of di and trifunctional polyoT~s, and the peel adhesion values were measured. The results presented in Table 5 show that the peel adhesion values decrease with an increasing NCO/OH ratio.

NCO/OH* PEEL STRENGTH
RATIO N/cm 0.752 0.28 0.702 0.94 0.568 1.98 * Reactants 1:1 Mixture of Poly GTM 55-28 and Poly GTM
83-34 Polyols and PAPITM 2580 Polyisocyanate EX P~El2: Adhesives were made from a polyisocyanate having a functionality of 2.8 and a mixture of di and trifunctional polyols, and the peel adhesion values were measured. The results presented in Table 6 show that the peel adhesion values decrease as the functionality of the polyol increases. For this example, the addition of a t.rifunctional polyol (POLY
GTM-83-84)increases r_he polyol functionality and decreases the peel adhesion.
TASLi; s Poly GT"' S5-56' Poly GT"' 83-34b NCO/OH PEEL STRENGTH
Ratio' N/cm 2 5 90.25 0.755 2.50 50.63 41.15 0.756 0.56 90.51 0.733 1.74 50.96 41.04 0.732 0.77 a. Poly GTM 55-56 Polyether, functionality 2, 45% ETO
content, MW 2000 b. Poly GT"' 83-34 Polyether, functionality 3, 70% ETO
content, Mw 4700 c. PolyisoCyanate PAPIT1" 2580, functionality 2.8 EXAMPLE 3: As noted above, the hydrophilicity of the polyurethane adhesive depends upon the hydrophilicity of the polyol. Thus, polyurethane adhesives prepared from polyols having high ethylene oxide content have a S much higher water uptake capacity as shown in Table 7.

EFFECT OF ETHYLENE OXIDE CONTENT OF THE POLYOL
Polyol ETO
Content NCO/OH Water Uptake Diisocyanate -Polyols _~_ % _.-- Ratio %
IsonateTM 2181 Poly G"" 83-84 70 0.756 571 PAPITM 94 Poly GTR' S5-56 45 0.755 282 PAPITM 94 XU:3r'" 15176 30 0.756 101 EXAMPLE 4~ A mixture of aliphatic isocyanates comprising 1.954 parts of DESMODURT'~ N 3300 (functionality 3.4-3.6) and 1.930 parts of DESMODURTM
W (functionality 2) were added to a mixture of 40 parts of Poly-GTM 55-37 and 0.0428 parts of dibutyltin d:ilaurate (METACURE'~M T-12) and then mixed with a stirrer blade which avoids a:ir bubble trapping. This mixture represented an NCO/OH ratio of 0.8. The mixing was continued at room temperature until a uniform mixture was obtained (about 2-3 min). The mixture started to build heat and viscosity after about 5-10 min after mixing. During this period of time, the mixture was cast on MEDIFILMTM 428 (thermoplastic polyurethane film) to a thickness of 40 mils, and immediately cured into an oven at 102°C for 5 minutes. The resulting adhesive was completely cured and showed a peel strength of 2.25 newtons/cm. on stainless steel, and had a water uptake of c>ver 200%.

FXAMPLES 5-8:
The formulations described in Table 8 below were mixed, coated onto the thermoplastic polyurethane film, MedifilmTM 428, and cured according to the procedure of Example 4. The adhesion and water uptake properties of the resultant adhesive laminates are described in Table 8 below.

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EXAMP1E 9: Polyurethane adhesive prepared for tape application. A NCO-terminated prepolymer mixture was prepared as follows:
A dry three-neck bottarn flask was charged with 77.2 parts of POLY GTM-26-37 polyol, 3.2 parts of DESMODURTM N- 3 3 0 0 , 1 c . 9 part s o f DESMODURTM tnr and 0 . 3 8 part of dibutyl tin dilaurate catalyst. The reaction mixture was then heated at 90°C for about two hours with stirring and under a blanket of dry nitrogen gas.
After the reaction was completed, the reaction mixture was allowed to cool to room temperature. To this viscous prepolymer, another' 6.3 parts of DESMODURTM
N-3300 was added with stirring to obtain a homogeneous NCO-terminated prepolymer mixture for preparation of polyurethane adhesives.
The polyurethane adhesive/non-woven fabric tape was prepared by first vigorously mixing 39.3 parts of the NCO-terminated prepolymer mixture and 60 .7 parts of POLY G'T'R-26-3 i' at room temperature for less than one minute. The reaction mass was then cast onto a support release paper to a thickness of about 6 mils. The cast material was then cured in an air circulating oven at 120°C for three minutes. After cooling to room temperature, a clear pressure-sensitive adhesive slab was obtained, which was then laminated to a thin non-woven fabric.
The lamination was performed by means of a standard rubber/metal nip-roll. The non-woven backed polyurethane adhesive tape had a peel adhesion of 1.2 Newtons/cm and a moisture vapor transmission rate of 1020 g/meterZ/24 hours at 37°C with a 90% relative humidity gradient.
Thus it is apparent from the foregoing description that the objects of this invention have been attained. A novel pressure-sensitive polyurethane adhesive has been invented which contains the desired properties.

Claims (38)

What is claimed is:

1. A pressure-sensitive adhesive comprising a polyurethane polymer formed by the reaction of an isocyanate component of formula R(NCO)n wherein R contains 4 to 26 carbon atoms and n is at least 2; and a polyol component containing at least 300 of polyoxyethylene having a molecular weight between 1,000 and 10,000, said components being reacted at a molar ratio of isocyanate moieties to hydroxyl moieties of less than one with at least one of the components having a functionality that is greater than two to facilitate crosslinking, said polymer having a glass transition temperature of less than 0°C, a moisture absorption at equilibrium of at least 20% of its weight, and a peel adhesion to human skin of between 0.3 and 4 newtons/cm width of the polymer; said polymer is crosslinked to a crosslink density alpha (.alpha.) of between 10-4 and 10-3 defined by the equation wherein i = 1 to n where n is the number of the reactant components Xi = mole fraction of i th component Fi = functionality of the i th component r = the NCO/OH molar ratio Mw = Molecular weight of the polyol.

2. The pressure-sensitive adhesive of claim 1 wherein the glass transition temperature is less than -30°C, the moisture absorbtion at equilibrium is at least 100%, and the peel adhesion is between 0.5 and 3.5 newtons/cm width of the polymer.

3. The pressure-sensitive adhesive of claim 1 wherein the isocyanate component is an aliphatic polyisocyanate and the crosslink density is between 2 x 10-4 and 10-3.

4. The pressure-sensitive adhesive of claim 2 wherein the isocyanate component is an aromatic polyisocyanate and the crosslink density is between 4 x 10-4 and 9 x 10-4.

5. The pressure-sensitive adhesive of claim 1 wherein the molar ratio is between 0.5 and 0.99.

6. The pressure-sensitive adhesive of claim 1 wherein the molar ratio is between 0.65 and 0.9.

7. The pressure-sensitive adhesive of any preceding claim, wherein the polyol is a homopolymer or copolymer polyether containing ethylene oxide or propylene oxide groups.

8. The pressure-sensitive adhesive of any preceding claim wherein the polyol component comprises a polyether polyol having a functionality of greater than 2 and the isocyanate component has a functionality of 2.

9. The pressure-sensitive adhesive of claim 7 or 8 wherein the polyol component is a polyether diol or -triol containing at least 30% by weight of ethylene oxide groups.

10. The pressure-sensitive adhesive of claim 7, 8 or 9 wherein the polyol component is a hydroxyl terminated prepolymer.

11. The pressure-sensitive adhesive of any preceding claim wherein the isocyanate component is an aliphatic or aromatic diisocyanate or a combination thereof, and the polyol component has a functionality of greater than 2.

12. The pressure-sensitive adhesive of any preceding claim wherein the isocyanate component is an isocyanate terminated prepolymer.

13. A medical article for application to skin which comprises a layer of the pressure-sensitive adhesive of any of claims 1 to 12 and a backing material. in contact with at least a portion of one side of the layer.

14. The medical article of claim 13 wherein the backing material is a natural or synthetic fiber, a woven or non-woven fabric, paper or a thermoplastic.

15. The medical article of claim 13 which further comprises a release layer in contact with the side of the pressure-sensitive adhesive layer opposite the backing material.

16. The medical article of claim 15 wherein the release layer comprises a material that does not securely or permanently bond to the pressure-sensitive adhesive layer.

17. The medical article of claim 16 wherein the material of the release layer Includes a silicone coating.

18. A medical article for application to skin which comprises a backing layer and a layer of the pressure-sensitive adhesive of one of claims 1 to 12, on at least a portion of one side of the backing layer for contacting the skin and securing the article thereto.

19. The medical article of claim 18 further comprising a release layer for protecting the pressure-sensitive adhesive layer wherein the release layer may be removed prior to use thereof.

20. The medical article of claim 18 further comprising a moisture or water absorbent material positioned for placement upon a moist or wet environment, wherein the pressure-sensitive adhesive layer is located adjacent at least a portion of the absorbent material.

21. The medical article of claim 20 wherein the absorbent material is in the form of a disk, and the pressure-sensitive material layer is associated with and at least partially surrounds the perimeter of the disk.

22. The medical article of claim 21 further comprising a support layer for the absorbent material.

23. The medical article of claim 22 wherein the pressure-sensitive adhesive layer is attached onto at least a portion of the periphery of the support. layer and completely surrounds the perimeter of the disk.

24. The medical article of claim 18 further comprising an attachment member for connection to another medical device.

25. The medical article of claim 24 wherein the attachment member is configured and adapted to receive a bag or container.

26. The medical article of claim 22 wherein the disk includes an aperture therein to permit passage of a fluid there-through.

27. The medical article of claim 26 further comprising means for joining the pressure-sensitive adhesive layer to the support layer.

28. The medical article of claim 27 wherein the pressure-sensitive adhesive lager is ultrasonically welded to the support layer.

29. The medical article of claim 13 or 18 in the form of an ostomy device, a wound dressing, a medical tape, a bandage, an incontinence device, a dermatological device, a transdermal device, a surgical incise drape or an intravenous catheter securement device.

30. A method for making a pressure-sensitive adhesive as defined in any of claims 1 to 12, for application to skin which comprises:
providing a mixture of an isocyanate component and a polyol component at a molar ratio of isocyanate moieties to hydroxyl moieties of less than one;
selecting at least one of the components to have a functionality that. is greater than two to facilitate crosslinking and reacting the isocyanate and polyol components in the presence of a catalyst to form a polyurethane polymer- having a glass transition temperature of less than 0°C a moisture absorption of at least 20% of its weight and/or a moisture vapor transmission rate of at least 300 grams/meter2/24 hours measured at 37°C and a 90% relative humidity gradient, and a peel adhesion to human skin of between 0.3 and 4 newtons/cm width of the polymer.

31. The method of claim 30 which further comprises casting the mixture upon a substrate and heating the mixture at a sufficient temperature and for a sufficient time to form a layer of the polymer.

32. The method of claim 31 wherein the mixture is heated to a temperature of between 100 and 150°C for a time of between 1 to 25 minutes .

33. The method of claim 30 which further comprises providing a polyether polyol containing at least 30% by weight of ethylene oxide groups in order to form a polymer having a moisture absorption ate equilibrium of at least 20% of its weight.

34. The method of claim 30 which further comprises forming an isocyanate terminated prepolymer by reaction of a portion of the polyol component with the isocyanate component prior to reaction of the prepolymer with the remaining polyol component:.

35. The method of claim 30 which further comprises selecting the polyol. component to have a hydroxyl functionality of greater than 2 to obtain the desired crosslink density.

36. The method of claim 30 which further comprises selecting the isocyanate component to have an isocyanate functionality of greater than 2 to obtain the desired crosslink density.

37. The method of claim 30 which further comprises providing the polymer in the form of a layer upon a backing material.

38. The method of claim 37 which further comprises providing the polymer in the form of a layer upon a release layer.