Stiffening of the cardiac wall by coronary blood volume
increase : a finite element simulation
Citation for published version (APA):
Huyghe, J. M. R. J., Arts, M. G. J., Campen, van, D. H., & Reneman, R. S. (1990). Stiffening of the cardiac wall
by coronary blood volume increase : a finite element simulation. In Biomechanical transport processes / Ed. F.
Mosora (pp. 23-30). (NATO ASI seires. Series A, life sciences; Vol. 193). Plenum Press.
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Published: 01/01/1990
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SflTFF'N\IING OF TTIE CàRDIAC !{ALL BY @ROM\RY BIOOD VOII]ME TNCREASE: A fliNITE EI.ANNW SÏM]LAIION
Jacques M. Ilt4rghel, Ttreo Arts2, Dick H. rran canpen3, ard Roberts S. Renernan4
Departlents of Movernerrt Sciencesl, Bioptrysics2 ard Physiologf
University of Limburrl, I4aa.stric*rt, tJ'.e Netlrerlards ard Detrnrbnent of
Mechanical Hrgheerfug3, Eirldtlcnren UniversiQr of Tbchnology
Eirdhoven, tlre Netlrerlards
ABSTRACI
A porous nredir:n finite elenrerrt nrodel of ttre beatingr left ventricle is usea Co simul-ate the jlfluence of tlre irtracororanlr blood voltmre on left
ventricular mectranics. fhe sporgy rnaterial is ccrposed of ilconqrressiJcle
solid (myocardial tissue) ard incorpressible fltrid (corornrlr blood). fhe
model is-axislznunetric ard allcrus for finite deforrnation, ilcludiJrg torsion around tlre axis of slnrnet4z. Ttre total stress in ttre tissue is ttre sun of
the intramyocardial pre.ssr:re, effective trnssive stress due to myocardial
defornation ard the óntr:actile fi-ber stress. Ihe ncdel is able to si:nulate
a ful1 carrCiac rycle. Ttrree-dilerrsional erd-systolic deforrnation conptrted
relative to tlre erd-diastolic state is strcrrn to be consisterrt wittr
o<peri:nerrtal data frorn tlre literiature. The direction of rnaxirnal shortening variea less tlran 30' from erdocarrdiun to epicardir.un raÈriIe fiber direction varied by nrore ttnn lOO'. ït is strcnm that tlre verrtricul-ar nrodel Qdli-bits
diastolió stiffenirg folJ,o^rirg an jrcrease of intracoronary blood voltune.
Enddiastolic left ventricrrlar pressure increases frqn 1.5 kPa to 2.0 kPa
wtren r:aisirg intracoronarlr blood voIurc from 9 to L4 ml per 1-00. g
myocaadial Lissue. the rncdel si-rnul-ation suggests lfnt the nrectranisn
underlybg tlp increase in erddiastolic pressure at higher coronarT blood
volune!, ís an ilcrease il trnssive stiffness of the rnyocarrdial fj-bers. this i:rcreased stiffness is the combiJred result of an c /er:alI increase in strain
in myocarrlial tissue ard tlre non-ljnear stress-strain relationstrip of
myocarrCial tissue. Keyuords
r-eft ventricle / poror:s rediun ,z mixture / erectile properti-es / díasí-:ore / coronanY perfusion.
I}IIROUJSIION
The carriiac wa1l is a conpler< biological stnrcture coneosea of
different conqrcnerrts: muscle cells, corona4r vessels, collagen filcers,
Biomechanicql Transport Procxses, Edited by F. Mosora eÍ 4/. Plenum Press. New York, 1990
i-ntracel1ular ard interstitial f1uid, 11nph ard blood. For tie sake of sinplicity, rnany autlrors of cardiac ncdels assurre tire cardiac waII to be a
hornogenous contirrlnun of sol-id rnatter. Tlre aim of t'tris sbudy is to
irrvesti-gate to vÈridr extent a rpre detailed nrcdel description of ttre
myocardiai tissue, jrcludirq a solid ard a fluid ccnponent, is able to
descri-be the stiffenirg of the cardiac walt by coronaq/ blood volune
ilcrease.
MEITION
l4aterial npdel. t{e assr-uned that myocardial tisstre r/as a q)orgy
stnrsture filled with intr:acor.ornry b1ood. Ihe rnaterial of vrtrictr the
sporgy strusture was rnade ard tirc intracororlarlr blood were both assured to be irrconpressilcle. Therefore, ctrrarges il voh:re of tlre solid fluid rnixtr:re were equal to the ancunt of blood beirg sqleezed out or sucl<ed in. ïhe
stress in tlre mixture was tlre sr-un of the intramyocardial pressure p
(present irr both fluid ard solid), effective trnssive stress due to ttre
deforrnation of the porous strusture ard contractile fi-ber stress. As tlre
collagen weave is three-di:nensional, we assuned ttrat tlre passive effestive
stress was tfrree-dinrensional. Ttre contrastile fiber stress, hcwever, asted
only in the fiber direcbion, which charqed aqross ttre raral-I. The contrastile
stress was tirne, str:ain ard strain rate deperdent. ïhe redistrilcution of
intramyocardial blood in tàe coronary bed was nrcdelled by Darqrrs 1aw: the
f1ow of irrtracoronar1l blood was proportional to tlre intramyocarCial
pressure gradient. ïhe proportionality constant is ttre pernreability of tlre
mediwn. In order to account for ttre drarqes il vascular resistance rrhen
irrtracoronary blood vo}.urp clurges, ttre perneability of tlre nrediun was
adapted proportiornlly to ttre square of ttre intramyocarraial coronary blood vol-r:nre in ttre course of the
corncrrtation-Fig. 1 Left: cross-secti-on of the rotationatl-v svnmetric fj-nite elsnent
nesh of a canirre left ventricle. ÀIl el&rerits contain contracti-l-e
flbers except ersrents 10, 11 and 12 whjlch represent the anrru-lus
fibrozus. Right: in a cross-sectj-on of the wa'l I of the teft
ventricle, the sequence of orrset of contraction is si-'rn:-l_ated to radiate frcrn a pojnt M (tinxe in rns).
Nunerical approactrr. The myocardial waII was subdivided into thirer
rirg-sha@ elenents (fiq. 1). Each elenerrt trad eight nodes. rhe ctrrarge G
position of-eactr node relative to the reference situation raras descriJced by a radial, axial ard circr-unferential displacenent at any tinre dr:rirg t]le
cardiac cycle. Quadratic intertrrclation yielded displacanents at
Íntermediate points. The intramyocardial pressure field was obtained by
linear interpolation from pressure values at the corïler nodes. Ttre total
nunber of degrees of freedom wàs 395 (351 displacenerrts ard 44 pressures).
fhite defornntion was accounted for by nreans of a totar ragrargian
z +
For tlre sake of rdiac wall to be a
his study is to
:scription of the
onent, is able to
:rary blood vol-une
;ue rdas a q)orgD/ ia1 of wtridt ttte re both asstuned to olid fluid nLórre
or sucked in. The
ardial pressure P
stress due to the
:er stress. As the : passive effective ss, hcrnever, acted -1. fhe contracEife
redistrilcution of y Darcryts 1aw: the re intrarnyocardial nrneability of ttle
ar resistance whert
of tlre nredir.m was lial cororn4r blood
r i r F l n i * a o ' l m n f
mtain contractile
)resent the anrrulus
waIL of the left
ln is sinul-ated to
ivided into thirbY
cdes. The c}rarqe in on was descri-bed bY ny tinre dr:rirg the
dispJ-acenents at
Ld was obtained bY
r nodes. the total ard 44 pressures).
r total Iagrargian
\
\
a p p r o a c h . A n i - r p l i c i t - o < p t i c i t t i r r r e . i n t e g r a t i o n . s c t r e r r p w a s u s e d . w i t h i l 1
each tine step a noaitiá Newbon-Raphson ite::ative procedure was used to
Gunt for the non-ljlearities ilctuded il ttre rpdel'
The axial and circumferential displacenerÈ of t].e 7 top nodes of -the
n e s r r w e r e s r 4 p r e s s e d . N o b l o o d w a s a l l o m l e d t o c r o 6 s t } r e e r d o c a r d i a l s u r f a c e . A t t h r e ' ' e r d o c a r r c i a l s i d e o f e l e r r e r r t s ] . t o g a u n i f o r m intraventrj-cufar p-v was appfi-ta as an e>rtêrral load' rtre loads ocerted by
tlre papillarlz mlscles ard'-by the pericardir.un were negtected' Alorg the
epicardial sr:rface we al-loued fiee of blood between the
;Ëir""q1*.t if"1
"oro.rty vessels
ard tl.e epicarrlial coronaaY vessels'
Initiation of
"o.,tt Jioí was not simultaneous for all
sarcollpres (fiq' 1) ' Ihe depolarisatj-on wave noveo from erdocar"dir-un to epicardiun ard frcm the apical region t o,"J trr" basal region. Ttre wave r€eded abort 40 ms to reactrl ;Ë;d"'ieft ventricul,ar r,rall.- rhe jnitial penteability of T" P":gf nedirun was derived tiÀ-aaga on tine constants of the coron;lrlr circufati-on
ard equal-s 2 nrn, iÀ:rr-r. Àe initial porosity of ttre rnedir:rn (= the
o e r . c e n t a q e o f i n t r a m y o c a r r c i a l s t r n c e o c c r : p i e d b y c o r o n a r l r b r o o d a t 0 k P a perfusion Pressure) is 6?'
The transm'ral variation of fijcer argle was derived from e4teriÍrental d a t a o f s t r e e t e r u ' ' a g u ' " ^ ( L 9 7 3 ) . T t r e S a r c o n e r e r r p d e l u s e d i n t } r e sjmulations is descrjlced elsevtrere (Htry$e' 1?891 ' Ttre trnssive constitutive betravior:r of tl.re *yo"utai-f tissue t""- á +r"=i-1íFár viscoelastic law wittt
an e4:onentiar eraJtic ,"+r"=", \,hictr *u= ritt a to ope,rimerrtal data of v-t ià,-:tqo, et a1 (1982), ard Yil et a1 (l-987) '
T h r e e c o l l r l t a t i o n s w e r e p e r f o r r r e d . E a c h c o r y l t a t i o n s t a r t e d w i t h a n
increase ot :ntracoiornry blóod volr.lre. The i'crease eq*alled 3% of the
myocardial vol.one io tfr" first .o*prrtiiio.t, 5,5eo in the.seconn corp,tation
ard gZ i5 the tfriá-conputation. Aiter ttre jlsrease of intracoronary blood
voltune, the i-ntraverrtricular pressure was ilcreased up to 2.5 kPa in all ttrree conputati".r=.-iit^fiy ttre tfrira corq>'tation yas. repeated, loadirq the ventricle onfy re to t kfá, ard tlren consecutive beats were initiated' The duration of ttre cardiac qgcles was 0'55 s'
A connercial post-processirq package I-DEA'S Í?F"tE -"1 Qgrnmics
Research Corporatioi| produced coÍor-coaeá plots of different local ortput
variables. To facilitate the ccnparison of conquted strails with
;re"tin*rt"l strajn data, lrcal trrree<inereiornl- Greerl strain tensors s/ere conputed witrr rereience- to tne erddiastolic state ard were irrter-preted in terrns of tneir
"ilerwalues (the principal
s!r?ins) a$ eiOervectgrl $ne
principal axes of
-strai')
. 'ihe ttrree principal strains were rariked from snall-est (nrost negative) to larrEest (nrost positive) '
RESUT,TS
Diastolic stiffness. The il"lcrease in irrtracoronarY b1d voltme
il1a'rffif wall thicrsre.ss. lïre pressure-vorure curves
resultirg frorn tr," uo." conprtations (fis. 2)- sho^r that diastolic
stiffness i'creased wit1. i'creasirq coronai vascrrlar volute' At a givert
left ventricurar vor'trme left ventricular pressure increased frcm t'5 kf^to
2. O kpa wtren raisirq blood- voh.une frorn 9 to 14 rnl per 1o0 g
left verrtricle.
Ttre cardiac cvcle. Rjection fractions for the three caldiac qlcJ-es were 5g2,55? ard 5 Z. a1,,e ijr,r" co.,r=e of the radial ard axial displaceuent confonent of all nodes of the nrestr is strcx'in in fig' :'
1 2
o]uronuiuuo*,i, ,, ó ivtrvrlv)rvol/
Fig- 2 Sjmulated pressure-volure relations of the passive left ventricle
at different revels of intr:amyocardiar brood volure. The
ventricul-ar__!ía11 qqiffens at ilsreased intramyocaruial blood
vo}.:nre. voLV ard vLV are tl:e initial ard currerrt intracavitanz voltune of tlre left ventricr:.lar urodel respectively. nB i= t]-e ratió of coronarlz vascular volune over total rnyocardial voh.une.
Fig. 3 Simulated successive states of deforrnation of tàe left verrtrj-cie. A
conputer generated picture is shcnrn of the deforrnation of a
meridional section of the nrcdel (dotted line : refererce state,
contirruous lile defornred state). Fïom left to rigfrt:
"r-l diastole, besinnins ard erd of ejection ard begirrLirg of díastole.
the circunferential displacenent ccnqrcnent (not strov,m) strcrued rotation of the aPo< relative to tlre base in countercloc]$^/ise direcÈion dqrirg the
ascendirg limbs of the ventricular pressure, wtrile ttre opposite napienea
durirg ttre descerdins rinÈ. lhe model ccrputed ircreasirg ern-qlsloric
values of tfie three principal strains with insreasirq depth (fig. a).
Erd-systolic prilcipal strails equalled 0.45t -0.01 ard -0.24 at 2/3
of tlre wa11 thic]<rress from the epicarditun ard.0.26, 0.00 ard -0.19 aE L/3
of the wa1l ttriclaness from the epicarrdiun. To arnryse the transrnrál
variation in the orientation of the prilc.itrui strain axes at tlre erd of
gjectior, we ccmputed the argle between tlre fi::st prilcipal strain axis
(i.e. the axis of rnaxi:na1 slrortenirq) ard ttre ci-rcrlnferential coordi5ate
z o
í
d
;sive left ventricle
btood volune. The
cramyocardial blood
urerrt irrtr:acavitanr :1y. nB is ttre ratià a.]. vo}.ue. re left ventricie. A deforrnation of a = reference state, :ft to ri@t: erd Lnrdrg of diastole. wn) stroved rotation
lirection durirg the
,e opposite happened
'easirq erd-systolic :ptà (fig. 4). )1 ard -0.24 at 2/3
00 ard -0.19 at 1-,23 yse the b:angnu::a]
axes at tfie erd of iJrcipal strail axis :erentia-]" coordi-nate
Fig. A rrànsrura1 distribution of erd-qlsto1ic prilcipal- str-aiJ]s as
-
predicted by tlre nrodel ard neasured bY l^taldnan et a1 (1985). In both nrodel
-ard
operi-nrent strajlls are given with respect to the
erd-diastotic
state-. EXPERIMENTAL DATA WALDIUAN ET AL (1988)
^.^ EXPERIMENTAL DATA WALDMAN ET AL(1985)
- FIBER DISTFilBUTION 1 - - _ FIBER DISTRIBUTION 2 --- FIBER DISTRIBUTION 3 A a r r i a
n
a -^ t a ^ L L----]
^ [
^ r l
L,^
- o-rffi
EPI
Fig.5 Ïhe arqle @ is the projection onto tlre epicardial.plane of the
argle betveen axis oi rnaxj:raf shortenirq ard tlre cirq.unfererrtial aiiection. The wariation of argle 4 with depth is plotted for three
fi-ber argle distributions, defiled jI table l-. Ttre two sets of
o,p"rimental data ( ^ a]ld a) are from two anjnals representirq tlre rarge observed in five dogs by t^tal&nan et a1' (1985) '
A I , A \ - : : - - - - A r
I
dj-restion. ïhe projection of this argle on tlre epicarrdial tarqent p1ale is refered to as the argle O ard is plotted as a funcÈion of á"ptrt at ttre irrterface of tlre elenrerrts 6t !8t 27 arrd. ttre elenrerrts 7, L3, Zf 1fig. S1 . The angle O shifted from -37' epicardially to -6' erdocardiallv.
DISCÍISSION
This studlz shcn^p tlnt (1) a bipÈrasic nrcdel of left verrtricr:1ar
nrechanics is able to conptrte an ilcrease of diastolic stiffne.ss by cororra4r
blood voh:ne llcrease, provided tiat tlre non-linear rpture of tlre
constitutive betraviour of nyocardial tissue is tal<en into accor:nt a15 (2)
the axisymnetric fhite elenrent nndel ccnputes qlstolic triaxial straiÉ
consisterrt with etperirnental data frqn ttre l-iter:ature.
Diastoric stiffness. when usirg quasi-rilear viscoelasticitlr,
stiffness ilsreases wit]" increasirg coronallr vascr:lar volture (fig. 3). Thi;
result is consistent wittr eperimental data of olsen et ai_. -(rgdr) arxi
Vogel et al. (1982) (fiq. 6).
T X P E R I M E N T
tr r Fotasstum arresfed {Olsen et at.1981 ) N=10 d o [cntroi I ) í V o q e l e t a l 1 9 8 2 ) I ' t . 4 ^ a P c s i l s r h e m t r , -- / t i 5
*
' 1 4 L "/4\/:
R=,r^1,171Í,'
, - t''' a/ t ' o 1 o 0 +----{---i oao 0 5 0 1 0 0 1 5 0 { m m H g ) 015 ^ BFig. 6 The left panel strours ttre deperderry of erd-diastolic reft
verrtricular pressure (LVp) on tlre coroÍraq/ perfusion pressure
(CPP) at a given cavitlz voh-une. Ttre right parrel shctrs ncdel
results of left ventricular pressure es a funcAion of
iatracoronary blood vo]ure at constant cavity volune. Stiffenilg
of the cardiac wall by insrease of corornry vascul_ar volune iÁ
more pronounced at higher caviQr voJ-r:nes, in both elperirnerrt
(Ieft) ard nrodel (right).
on the basis of the e>peri:nental qr:antification of ttre relationstrin of
coronarlz perfusion pressure ard intracoronary blood volure by Uorgenstern
et a1. (1973), we ilfer tbat the ttree va}ues of irrtracoronanr blood volune chosen in fig. 3 correstrrcrd with coronarl/ pe.rfusion pressures-of 6, l_l-, ard
14 kPa. rhis i:rplies that the ncdel predicts ttnt at constant caviw
vohne, left ventricular pressure ilsreases frcrn 1.5 kpa to 2.0 kpa whó
raisirgÍ perfusi-on pressure frorn 6 to 14 )<Pa. the sane strift of cor.on1nz
2 A
( k P a J
ial targerrt plane is J-on of depttr at the 7 , L 3 t 2 8 ( f i g . 5 ) . ardia1ly.
)f lefb ventricular 'tiffness tryr corona4r
ear nature of ttre
i-nto account ard (2) Lic triaxial strains
lr viscoelasticiQr, ohnne (fig. 3). ïtris r et al. (l-981) ard "/"'4
-Ï--1
t
i
1 015 nB erd-dia.sEolic left perfirsion pressurepanel shcrus npdel
s a function of volune. Stifferdry wasorlar volune is in both operi:rent ttre relationstrip of 'ltrne by l,Íorrgenstern )ronarT blood voltune ;sures of 6, 11, ard
at constant cavity
cPa to 2.0 kPa lrihen : strift of cor.onarlz
perfusion pressure carlses an iscrease i1 lefb verrtrio.rl-ar pre-ssurê fr"on L'5 il-;.4-kl'.'in potassir-un arrested hearts accorràirg to tlre eryerlnertar !a! oi Ofro, et a1l (19Bl) , vÈri1e Vogel et a1. (1982) fird an i'crease of left veritricular pressure ii*, f b f.a kPa ard from 3 kPa to 3.8 kpa in intacb
;*r1" irdicatilq that ncdel re.sults are \,/ithin the l..r'ne of val-ues
Ë-="t a operinentally. The i'crease in !ta1} ttriclsress irduced by the
i[""="a i:rt
"""r"rrri blood volme
is consisterrt with tJle operirental
art^ of Morgenstern
"€ .f. Q973). One might be Fnetea
to attribute the
str:ift of the pressure-vol-r-ure cr:rrre to tfre láft in fig. 3 to ttre ilcrease in wa1l ttriclsress, on the basis of Iaplacers law. Hcn'rever, it is not eVident ifr.t f..ptu""ts law applies to biptnsic rnaterials. In a sirgle trfnse solid roai"riai, ilcrease
-in
thiclsresl of the strell irduces an increased
=titfrr."t of tlre she1l, because more naterial is available to take tp shell
forces. In the case of a solid-f1uid nLixture, addirtg nrcre fluid to t}re
miJ<b-rre, does not result i1 additiornl rnaterial- to take rp shell forces'
Tensj-le forces can only be borne bY tl"re solid. _ Ïtre il1crease in
Gt-^"ororrty blood volune- resulted in increased 1Ë11 thiclg1ess, krub not in ir-r*""a stliffness wtren we replaced the quasi-li-near viscoelastic law by isotropic linear elasticiQr !\]trille rnaintailirg Darqfts law as a description
;;;--ái" redistribution of intracorornry blood. These resul1s shcnr that
rtittorirg of the diastolic left ventricle by coronaaT blood voltme
increase strould not be irrterpreted in te11ls of Laplacets law' but rather as the conrbhed resul-t of an oir"r.ff increase in strail in myocard-ial tissue utra tn" non-linear stress-strail relationstrip of ttre myocaldial tissue.
Ttre cardiac cvc1e. The npdel conputes ilcreasirq values of sf;:ajn with incr"asn'tq depth. I,'Iany eperjnrental data frcrn the fiterature point in the *n* ait".tion. fn tif. a-we have used the operirnental data of l^Ialdnan et
aI. (l-985) to a.ssêss the transrn:ral distribution of principal strain as
preaitUeA by the nrodel. Althor-lgh tlre direction of rnaxj:rnl stress alrrpst -coinaic"=
wlt]- the fiber direclion, the direction of naxirnal strorterirg
(i.e., ttre third principal strain axis) does not. Asross tlre wall tlp
à,e"i.a d-irection of rnaxjrnal strortenirg does not v-ary. nearly as muctr,as
t]lJ muscle fjlcer direction (fig. 5). ttris firdfuIg is consistent wittr
eryerinrental data of killzen et aI. (1984) ard l{aldnan et a1. (1985). Ihe
taiter jrnrestigators fourd that ttre abclre defiled argle 4 of rnaxirnal
strortenirg equaled -22+2L" jl ttte jlner tralf of tlre wa1l (65!9? of ttre wall thiclsress from tlre epicardirm) . A conunon feab.rre of the nrcdel prediction
ard ïfatdnants data is tfre progressive rotation of ttre principal axis of
shortenirq tcnrards t].e circr.unferential direstion with increasirq depth. @NCIUSION
An axisrTnu'netric two-phrase finite elenrerrt nrodel is used to simrfate myocardial defornration a"iitq the card.iac rycle. ColÍqrÊed tr:ansrnrral straiJl dLstrj5ution is in agreemerrt witJ: e4rcri$enta1 data frcm t-l-e literature.
The ncdel irdicates ttat tle increase in diastolic stiffness by increase of
coronaay vascul-ar voh-une stroul-d be interpreted as a cclnbifred effect of an
overall- hsreased strail in the rnyocardial fi-bers ard tlre non-lirear
stress-strain relationships of ttre myocardial tissue.
Qrestion from t].e audience: rsnrt axislnmnetrlr a rattler rough appr:oxi:nation
@ of t]le left verrtricre?
tfu1ghe: We ctrose for an axiqarnretric rncdel il order to reduce conpr-rtation ti-t. fn:-s approxi:nation is irdeed a limitation of this nrodel. In decernber' our grol4) wili present a three-dinrensioral nrcdel of the left ventricle at the Wjnter Annual Meetirg of the
A,SI4E-Ë*
Q'rcstion from ttre audience: Hcnr do you analyse torsional- defornation with an axislarmetric nrodel?
Hryghe: Ïhe finite el-enrent code &rat Íie usê has been r^rritten speciarly for
finite deforrnation incl'dirg t"Ài"". bccept a rad'al ard
axiaf
dirylacenrent, ttlere is al-so a-cirqmterentiar displacenent,
\dtlictr is also axiqprunetric.
oddou: There is an essentiar d.ifference--b.pg, the poro's nrediun approach
of your gïoup arxi our gn:oqp, b""""""
{1uid in y.rr -*}er
is ttre coronary blood, raÈrire in o'r arnlysi"'it i" trr. itt .titíJri"à
ttuyghe: This is
"ï{^.1*!: fr: y". ÊrenCIrena have also verlz different tinre constants ard ttris is raÈry we feel i€ ir
""""plJi"-i"-".gr".t intêr:stitial fluid flcni il our analysis.
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