Ernst-Peter Nikolaus Panagiotis
Strecker, Freudenberg, Tsikuras,
MD #{149} Dieter Liermann, MD #{149} Klemens H. Barth, MD MD #{149}Georg Berg, DVM #{149} Michael Westphal, MD MD #{149} Michael Savin, MD #{149} Beate Schneider, MD
Expandable of Arterial Experimental Work
Arteries,
extremities,
grafts
#{149} Arteries,
and
stenosis
92.456,
prostheses, or
92.456,
S
types of vascular prostheses have been developed and successfully implanted into the iliac and femoral arteries of patients (1,2). The data published on those devices are very promising, although longEVERAL
1990;
From the Departments Nuclear Medicine (E.P.S.,
nal Medicine (H.R.D.W.), Diakonissenknankenhaus Kanlsnuhe-R#{252}ppunr, Diakonissenstrasse 28, D-7500 Karlsruhe 51, Federal Republic of Germany; the Department of Radiology, Univensity Kliniken Frankfurt, Federal Republic of Germany (DL.); the Department of Radiology, Georgetown University Hospital, Washington, DC (K.H.B.); the Institute of Pathology (N.F.)
and Veterinary
Hygiene
vensity Clinics Freiburg, Germany; the Department Krankenhaus NeukOlln, lic of Germany (MW.); Mass
(MS.).
Institute
(GB.),
Uni-
Federal Republic of of Radiology, St#{227}dt. Berlin, Federal Repuband Medi-tech Inc. WaFrom
the
1988
RSNA
an-
nual meeting. Received April 17, 1989; revision requested May 16; final revision received November 28; accepted December 8. Address reprint requests to E.P.S.
RSNA,
1990
the
There
are,
for in-
stance, self-expandable devices with certain degrees of elasticity and flexibility, and balloon-expandable stents of fixed or flexible shapes when expanded (3-11). The authors have developed a balloon-expandable prosthesis consisting of tantalum wire mesh that is flexible both in the nonexpanded and the expanded states (11). The purpose of the study was to demonstmate the flexibility and reliability of the balloon-prosthesis assembly with regard to introduction through curved arteries and implantation into femoral arteries near the hip joint and the thigh demanding adaption to movements of the treated vessel and surrounding muscular structures.
AND
METHODS
retract
balloon
from
of the
due to friction through
treated.
as well.
obstruction,
of Radiology and PT., B.S.) and Inter-
and
ity differ
the
stent
as they
ex-
angioplasty
during
the
catheter
introduction
introducer
sheath
or the
arteries.
The dimensions of the vascular prosthesis can be adapted to the required diameter
and
length
of the
The achievable
vessel
to be
diameter
of the
prosthesis depends mainly on the ben of loops per stent circumference
numand
the loop length of the metallic knit (Fig lb). The producible diameter of an expanded
prosthesis
ranged
mm, with a maximum Length and expanded prosthesis angioplasty
vascular
are related balloon.
prosthesis
from
2 to 14
length of 8 cm. diameter of the to the size Shortening
secondary
of the of the
to radial
ex-
pansion is minimized by mounting the prosthesis on the balloon with a pnimaniby reduced length (Fig lc). This is achieved by longitudinal prosthesis compression of the loosely connected metal loops.
Animal
Studies
Twelve
prostheses
the femoral
were
arteries
implanted
of 10 dogs
15-30 kg. Each prosthesis and 5-6 mm wide in the
into
weighing
was 2.5 cm bong expanded state
Description
of Prosthesis
(four loops per circumference; loop length, 1.6 mm). To spare the femoral artery from injury rebated to surgery,
The vascular ted of a single
prosthesis is a tube knitmetallic tantalum filament
surgical cutdown of the common carotid artery was performed with general an-
175:97-102
1
tion
curved
MATERIALS
©
#{149}
pand in the radial direction (Medi-tech, Watertown, Mass) (Fig 1). This mechanism prevents stent displacement from
term results are not yet available. The structure and material of those prostheses differ; hence, the method of introduction and their biocompatibil-
98.721
tertown,
MD
in Progress’
Index terms: 98.456 #{149}Arteries,
Radiology
R. D. Wolf,
Tubular Stents for Treatment Occlusive Diseases: and Clinical Results
The balloon-expandable vascular prosthesis consists of a flexible, knitted tantalum wire mesh tube. To demonstrate its pliability, this prosthesis was tested experimentally in 10 mongrel dogs by implanting it into the proximal femoral arteries. The maximum follow-up time was 1 year. On the basis of the experimental results, in which there was no relevant stenosis, occlusion, or mlgration of the vascular prosthesis, nine patients were treated: one with iliac artery occlusive disease and eight with superficial femoral artery (SFA) occlusive disease (four reocclusions after angioplasty and four unsatisfactory primary angioplasty results). One SFA lesion was treated with the crossover method from the contralateral side. All implants remained patent without hemodynamically significant stenoses, with the longest observation time being 6 months. Flexible, expandable vascular prostheses are promising adjuncts to angioplasty.
98.456 92.721,
#{149} Helimut
0.1 mm in diameter. Since the knitting is a series of loosely connected loops, this stent design tic and very
is, within certain limits, elasflexible, both in the longitu-
dinal and radial directions. Initially, the prosthesis was wrapped around an angioplasty balloon catheter and held there by means of its own radial tension. Then a new design for fixation of the prosthesis on the angioplasty catheter balloon was
developed.
The prosthesis
by thin-walled silicone end of the balloon that
and proximal
ends
is held
firmly
sleeves at either cover the distal
of the tubular
esthesia
(pentobarbital,
venously). Then the with a stent mounted
mm in diameter
25 mg/kg,
a
intra-
angioplasty catheter on a balloon 5-6
was introduced
over
a
guide wire through a 10-F introducer sheath. Under fluoroscopic control, the balloon was inflated for stent expansion
and placement near the hip joint into the common femoral artery (Fig 2) or into the proximal part of the superficial femoral artery (SFA). Two animals received implants
on
the animals
both
sides.
were
After
allowed
the
procedure,
to bend
and
ex-
stent.
During balloon expansion, the vascular prosthesis is released because the silicone sleeves shorten in the longitudinal direc-
Abbreviation:
SFA
superficial
femoral
artery.
97
c.
b.
a. Figure
1. Catheter-stent assembly. (a) The knitted wire-mesh tube is mounted on the expansion site of the its ends by thin silicone sleeves to prevent backsliding during introduction. (b) Draft view of an expandable distended tantalum wire ioops, which are without firm connection at their junction sites. (c) After complete sis becomes unlocked by minimal foreshortening of the prosthesis and the silicone sleeves.
5-F balloon catheter and held at metallic knit demonstrates the balloon distention, the prosthe-
tend their lower extremities freely; their moving habits outside or within the kennels
were
not
restricted.
During
the
pro-
cedume, the animals received 5,000 hepanin intraarterially. Thereafter, day for 5 weeks, the dogs received
IU of every 325 mg
of acetylsalicybic
acid for platelet-aggre-
gation inhibition mole to prevent
and 75 mg of dipyridaplatelet activation and
thrombosis.
Clotting
parameters
were
not
monitored (12). Control angiography was performed 1, 2, 6, 10, 20-30, and 54 weeks after implantation. One day and 1, 2, 6, 8 (two dogs), 9, 11, 15,
and
54 weeks
after
stent
implantation,
the experimental animals were killed to perform pathologic gross and microscopic examinations (Fig 3). For this purpose, the arterial segments treated with the prosthesis, distal
their parts,
adjacent
and
their
proximal
and
corresponding
con-
tmabateral arterial segments were memoved, longitudinally opened, and attached to cork plates with corrosion-resistant stainless steel needles, with their inner
vessel
surface
turned
fixation in 4% buffered least 2 days, the arterial
ed into thesis
3 X 4-mm struts
were
magnification to the
tic-van
On
the
standard
aid of
damage
a.
Paraffin
Figure
conditions slices
hip
of 5 jm and elas-
basis
arterial
of the
information
ob-
experiments,
20 patients
atherosclerotic
disease
were
had
lesions
of ili-
Eleven
patients mean
b. 2.
joint
Animal into
nine loops
lesions in those per circumference;
mm;
stent
these cases (11). In (seven
age,
stenotic
(arrows).
(b)
knitted Control
tantalum
stent
angiogram
years;
cm
[in
previously
2.5
and
lapse in one patient. One had an eccentric, high-degree
range,
two
stenoses
three
wom-
45-81
patients
5). That
stents
flexible The
residual
(Fig
Eighteen
patients (five loop length, 1.6
required
were
per
placed
patient
in
one
case,
8
Four patients had nestenoses of the after a previous angioplasty. Four pashowed an unsatisfactory result immediately after angioplasty of the SFA:
of
were
nine
cm]). SFA tients
plasty
prostheses
Radiology
(a) A 2.5-cm-long artery
were pubthe remaining
men
65.6
length,
four
#{149}
femoral
implantation.
the
98
the
after
years) with severe life-style-limiting claudication, the introduction of the prostheses or the anatomic site of implantation required a flexible intravascular implant. The length of the stenoses ranged from 1 to 8 cm (mean, 4.2 cm), and one to
(Table).
experiment.
of
implanted
the
near
same
animal
of its to be using
tortuosity. treated routine
the
2 weeks
staining.
ac arteries, and lished previously en;
layers.
to obtain hematoxylin-eosin
in animal
treated.
nine
the
to prevent
Treatment
tamed with
with
under
Patient
was
removed tissue
Gieson
at divid-
and the pros-
surrounding
was performed thickness for
After for
particles,
glasses
embedment
upward.
fonmalin tissue
and
proximal
access
by
due
right the
an
to
wall
dissection
arterial
SFA
wall
cob-
retrograde
arterial
lateral side 2-cm-long
(Fig 4). Another patient had stenosis due to a wall dissec-
tion,
which
occurred the
right
particular
puncture
of
4 days common
the
after iliac
vessel
a
10-F
a
ameter
on
angio-
mm
a
the
were less
than
stent,
the
a diameter
the
di-
equal
to
angioplasty of
more
than
completely
balloon
a a
with
balloon was
Since
expand
in-
through
arteries
expansion
diameter. not
the implant.
In
6 mm,
stent with
restenosis
implanted
sheath.
for
mounted
or
justified
wall-supporting
introducer
will
(x-ray magniOnly unsatis-
results
prostheses
artery
overdilation
angioplasty
for
were an-
diameter was artery diameter
image
angioplasty
balloons
artery
balloon to the
the film disregarded).
previous
diameter
the
without
The equal
was
dication
contra-
required
artery. to be
measured fication
All
with
because lesions dilated by
technique
of the chosen
after
necessitated
technique,
gioplasty
factory
of these patients stenosis of
that
crossover
in
stent arterial
with
diameter
April
6 the
was
1990
b. Figure
3.
specimen
(a) Gross
specimen
demonstrates
chosen
to be
the
1 mm
arterial
diameter
priate
fixation
of the
insertion
tmolled
formed
than
the
appro-
stent.
prosthesis
was
of fluonoscopy.
When
con-
the balloon-prosthesis assembly reached the arterial area to be treated, the introducem sheath was pulled backward to permit inflation of the balloon with thesis. In cases in which the site
treated
was beyond
the length
the prosto be
of the in-
troducer sheath (distal SFA), the balloonprosthesis assembly was moved, without protection of the sheath, through the amtemial lumen, even around the aortic bifurcation. Five thousand international units of hepamin were applied intraarterially before balloon inflation for angioplasty, and an additional 5,000 IU were given after insertion of the 10-F introducer sheath. Thereafter, an intravenous hepanfl
infusion
to increase
was
administered
for
the thrombin
time
3 days
to three
to
four times normal (with monitoring of the thrombin time). In addition, 325 mg
of aspirin
and
day
given
were
plantation
75 mg orally
of dipynidamole during the
follow-up
thrombosis
by
period
per postim-
to prevent
platelet-aggregation
inhi-
bition. The therapeutic effect of aspirin and dipynidamole was not monitored. According to the experimental protocol, penipheral arterial foot pressures were monitored before and after the procedure, at 4 weeks, and at 3 and 6 months (Fig 6). Foblow-up angiography was performed 3-7 days and 6 months after prosthesis implantation.
RESULTS Animal The
of the
affirmed
that
could be insertion
correctly at the
and
migration
All
that the
Volume
tantalum
175
animal
the
holes,
femorab mained
expeni-
manipulated chosen arterial
artery patent.
did
not
Number
1
take
place.
in the
removal
defects were or distally.
fects
appeared
implantation The
wire
after
mesh
in the pathologic
up to 2 weeks
me-
observed in These de-
first
and
few
weeks
resolved
after-
examinations
after
is covered
of tantalum
near the hip joint With angiography,
after wand.
knitted
channel
small filling the prostheses
implantation
me-
by neointima. struts
from
following months
tenial
neocclusion
remained
deformation
the
prosthesis,
as was Nine
ob-
later, a thin fibrous layer filled the openings of the wine mesh, while the stent was neointima. em, a thin,
layer
completely Eight and transparent
covered
the
covered with 12 months latendothelial
buminal
surface
of de-
the prosthesis fects, which
(Fig 3). The were observed
filling angio-
graphically,
corresponded
to thin
thrombus formations in the first few weeks, and later on, to an intimab layer. There was no significant foreign-body reaction to the tantalum implant. In general, theme was a mesomptive reaction in the tissue sunrounding the stent, with healed scar formation. In most cases, the inner third of the media was involved in this process.
Patient
Studies
All mectly
tantalum implanted
sites,
and
no
prostheses into the difficulties
during cases, were
an 8-cm-long penficial
insertion
and
by
were
con-
could
(Figs
4,
be further
the support of tubular (Fig 4). In one case, after
neocclusion
femomab
artery
of the occurred
opened support
su-
was
seen
due
were
by means provided
after
arterial
of the mechanical by the stents. No
stress
course
extremities tients were
tubular
wire
compression caused
of the
observed. to protect
The their
per extremities from severe mechanical stress (eg, blood cuffs).
traction
filling or with
digital subtraction which was performed after stent implantation. intravenous digital angiograms
are
lower paup-
outside pressure
No significant intrabuminab defects were observed within proximal or distal to the stent
intravenous ognaphy, in 1 week Six-month
or
by a curved
or motion
was told
me-
An 8afterpatent. that had
to a vascular
to external
mechanical
6 an-
completely
of the
due
angiwithsub-
available
for
two patients. In the first patient, with a stent in the proximal part of the SFA,
the
angiogmam
smooth filling defect thick) that probably en of neointima (Fig
ond patient, defects can common
en-
the stenosed arterial not fully opened
angioplasty
dilated prostheses
were arterial
collapse
mesh
weeks
performed immediate
an
stenotic
covered
microscopically.
microscopic
tissue.
peat balloon dilation therapy. cm-long prosthesis implanted ward held the arterial lumen In general, arterial segments wall
served
(b) The
the
angioplasty previously,
vealed a thin layer of thrombus spread over the stent. Six weeks after implantation, a complete neointima
by
after site,
The
and
5). In all segments
prosthesis
prostheses
#{149}
implantation.
countered
Experiments results
ments
after
neointima,
pa-
to achieve
of the
by means
newly
wider
tient’s The
of the SFA 1 year
depicts
no intraluminal be seen in the
iliac
artery.
a thin,
(0.5-1.0 mm represents a lay4e). In the sec-
The
filling treated ankle-arm
indexes remained unchanged during the follow-up period in those two patients. In the other seven patients, the ankle-arm indexes improved by the placement of the arterial prostheses and did not decrease within the first
4 weeks
sunements). improved
to 3 months
The ankle-arm in all patients
(four
mea-
indexes by more Radiology
99
#{149}
a.
b.
C.
Figure 4. (a) Severe short stenosis of the proximal part of the right SFA (arrow). (b) No significant improvement after angioplasty performed with the crossover technique from the contralateral side (arnow). (c) The catheter-stent assembly is introduced with the crossover technique oven the aortic bifurcation. (d) The lumen of the SFA is held completely patent after implantation of a vascular prosthesis
(e)
(arrows).
Intravenous
digital
subtraction
angiogram,
months after implantation, demonstrates patency. rows) is covered by a smooth layer corresponding
obtained
6
The prosthesis to neointima.
(ar-
d. 10%. The change in ankle-arm from before to after treatment was significant (P < .001 by the Wilcoxon signed rank test) (Fig 6). Clini-
recoil of the arterial loon dilation, which stenosis on occlusion
cal symptoms
treated arteries may than with angioplasty arterial flow through increase. Furthermore, regular inner surface
than index
with
an
in all but improved only.
improved
unlimited
one
permanently
walking
patient,
maximal
who walking
distance
had
an
distance
fore,
with
Intraarterial stent placement optimizes the mechanical alterations caused by angioplasty. The mechanical support of the distended tantalum
100
prosthesis
.
Radiology
prevents
the
luminal
an elastic
wall after can result (1,11,13).
cross
prosthesis
irregularities vessel lumen.
DISCUSSION
mesh
the
ment treated in reflected
section
babin meThemeof the
become widen alone, and the the vessels will a smooth and is achieved, diminishing
wall
protruding into the This reduces pressure
gradients (1,11) and, lence as well. However, noncompliance
e.
of the
probably, the arterial
by the stent wave patterns
turburelative seg-
may result that could
disrupt
normal
The
design
sis offers
flexibility. even with
flow
patterns.
of the
a high
degree
Therefore, a length
can be introduced sertion through
knitted
prosthe-
of mechanical
this implant, of 8 cm (one case),
into curved
the SFA. arteries
oven the aortic bifurcation The prosthesis can maintain figuration after expansion,
Inand
is possible. its consince the
loosely connected loops, made of tantalum wire filaments, are elastic within certain limits. The maximum radial compression tolerated by the prosthesis amounts to 40% of its oniginal shape. Therefore, it becomes evident
that
the
knitted,
semiebastic April
1990
corrosion sue fluids are
caused (16-17).
covered
by
tantalum electrically preventing
by surrounding tisTantalum implants a thin
layer
pentoxide, negative adhesion
are negatively A mechanical and stainless the same diameter strength) resistance
of inert
which creates an surface charge, of platelets that
charged
as well
(18).
evaluation of tantalum steel stents knitted in pattern (wines of the same and the same tensile revealed no difference in to compression.
Animal tests not yet published meveal that tantalum, like medicalgrade stainless steel alloys, can be megarded as thrombotic resistant. Our tantalum implants are chemically electropolished to achieve a smooth surface, preventing uncontrolled thrombus formation. Immediately af-
ten implantation, b. Figure 5. (a) Severe dissection of the common planted flexible stents open the curved arterial travasation due to the dissection is seen.
iliac artery after angioplasty. segment completely. A small
(b) Two
im-
amount
of ex-
long
SFA
with multiple any angiographic changes
the
stents
related Since
movement
osseous a knitted
of
or muscular wire-mesh
prosthesis consists of loosely connected loops forming a nonrigid elastic structure radially, arterial compliance will probably be only minimalby disturbed, reducing the tendency of thrombus formation. According animal experiments performed to study various vascular graft mateni-
als, by using ance
preoperative
measurements
oxine-labeled good before
immediately
1 MOnth
Stent
after
after
Stent
Stent
Figure 6. Doppler pressure ankle-arm indexes as percentages in all patients before, immediately after, and 1 month after stent placement (M mean, ±1 standard deviation).
prosthesis
opposes
cient
and
force
compression
itself
with
elasticity
suffi-
to outside
to prevent
the
conforms
hip,
because
to arterial
the
prosthesis
curves
induced
by flexion
or extension
extremities. alterations prosthesis
Secondary intraluminal due to the bending of the were not observed. In pa-
Volume
175
Number
#{149}
of the
1
lower
indium-i
there
between
11-
is a
elastic
properties and graft patency (14). Our dog study results demonstrate that the percutaneously inserted prosthesis will initially be covered a thin layer of thrombus that will almost completely endothelialized
by be
nied
by
a small,
hemodynamicalby
degree
of luminal
oroscopy
due
to its high
proton number. ed as biologically
Tantalum inert
density
is regardand shows
me-
intimal
by platelet-de-
of a self-expandable
femoral
into
tenies. reveal should animals duced taneously stents balloon nience
Our animal experiments promising results, although it be noted that we used healthy without experimentally inatherosclerotic disease. Percuimplanted expandable may extend the indications for angioplasty, and more expeis necessary to determine the
indications the
iliac
and
pros-
thesis
for this
popliteal
new
atherosclerotic
and
femomab
an-
therapy
for
disease
in
arteries.
U
References Palmaz
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plantation
1.
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not observe any occlusion developing after a follow-up of 18 months (11). Tmiller et al (20) reported a patency mate of 87% 9 months after im-
nan-
rowing. Tantalum is better suited to the specific needs of arterial stents. This metal is superior to stainless steel or other alloys because it is very radiodense and is well visualized with flu-
layer
nived growth factors (4,10,20). The mesults of our patient series are very promising; however, the follow-up time is still relatively short. In anothen patient group treated with this prosthesis in iliac arteries, we could
occlusive
within 2 weeks, as unpublished ebectron-micnoscopic examinations in dogs have revealed. This is accompainsignificant
collapse.
The results of animal experiments have confirmed that the prosthesis can be implanted into arterial sites
near
platelets,
correlation
to
compli-
and
on occlusion
hyperplasia
treated
did not reveal or mechanical
to the
surrounding
tissue.
segments
thin
to cover the metendothelial coven that may formation on the
prosthesis wall thereafter (19). Thrombosis remains a problem, causing acute occlusion and later stenosis
tients,
a very
thrombus develops al material, allowing cells to form a thin prevent thrombus
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