Ventricular assist devices for children
-
Upload
independent -
Category
Documents
-
view
0 -
download
0
Transcript of Ventricular assist devices for children
www.elsevier.com/locate/ppedcard
Progress in Pediatric Cardio
Ventricular assist devices for children
J. Timothy Baldwin a,*, Brian W. Duncan b
a The Division of Heart and Vascular Diseases, The National Heart, Lung, and Blood Institute. Two Rockledge Centre, Room 9150,
6701 Rockledge Drive, Bethesda, MD 20892-7940, USAb The Departments of Pediatric and Congenital Heart Surgery and Biomedical Engineering, The Cleveland Clinic Foundation, USA
Abstract
Infants and children may experience such severe heart failure that circulatory support is required as a bridge to recovery,
transplantation, or until other surgical intervention can be performed. While older children may be supported by devices designed for use
in adults, historically, options for pediatric circulatory support have been limited to extracorporeal membrane oxygenators (ECMO), short-
term centrifugal pump-based ventricular assist devices (VADs), and paracorporeal VADs. However, these devices present substantial risk
for adverse events in the pediatric population. To address the need for improved circulatory support devices for the youngest pediatric
patients, new devices specifically targeted to this vulnerable population are being developed. These include implantable rotary blood
pumps, compact cardiopulmonary assist systems, and extracorporeal pulsatile and rotary pumps for acute and chronic support. Several
devices are expected to be available for clinical evaluation soon. These devices will hopefully provide solutions for challenges that are
unique to pediatric circulatory support, such as the anticipated growing population of failing single ventricle patients who have previously
undergone a Fontan procedure.
D 2005 Elsevier Ireland Ltd. All rights reserved.
Keywords: Heart failure; Ventricular assistance; Cardiomyopathy; Pediatric and congenital heart disease
1. Introduction
Ventricular assist devices (VADs) are now reaching
relatively high levels of success for treating heart failure in
adults, as demonstrated by the growing bridge to transplant
experience which now numbers in the thousands of cases [1–
7]. The superiority of VADs over optimal medical therapy as
a treatment for late-stage congestive heart failure was
demonstrated in the landmark REMATCH trial. The trial
also provided clinical evidence for FDA approval of the
HeartMate VE VAD as a permanent ‘‘destination’’ therapy
[8–10]. Other VADs, including newer-generation rotary
devices, are currently undergoing clinical trials to achieve
similar approval [11,12]. In contrast, technological advances
in pediatric mechanical circulatory support have lagged well
behind. While the patient numbers are much smaller, the
potential in recovered patient-years is great considering that,
when given adequate support, the likelihood of long-term
1058-9813/$ - see front matter D 2005 Elsevier Ireland Ltd. All rights reserved.
doi:10.1016/j.ppedcard.2005.11.005
* Corresponding author. Tel.: +1 301 435 0498; fax: +1 301 480 1335.
E-mail address: [email protected] (J. Timothy Baldwin).
recovery is very high [13,14]. Today, the most common
approach to pediatric mechanical circulatory support is
extracorporeal membrane oxygenation (ECMO) [15–19].
This can be attributed to both a lack of alternative pediatric
assist devices and the extensive pediatric experience utilizing
ECMO for the treatment of respiratory failure. Despite its
widespread use, ECMO restricts patient mobility, presents
significant risks for adverse events such as bleeding,
thromboembolic events, and infection, and, as such, is only
adequate for short-term support.
The use of VADs for pediatric circulatory support has
been shown to result in significantly fewer long-term
complications compared to ECMO support [13,14]. Essen-
tially all pediatric VAD experience in the United States is
limited to a single centrifugal pump-based system. While a
greater number of alternatives are available worldwide, most
are pulsatile, paracorporeal devices, that are not fully
implantable for the majority of children [20–24]. Clearly,
the limited options for mechanical support of the failing
circulation continues to be one of the major issues in
pediatric cardiology and cardiac surgery.
logy 21 (2006) 173 – 184
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184174
2. Challenges in pediatric mechanical circulatory
support
2.1. General considerations
The most obvious consideration in the design and
development of circulatory support systems for children is
patient size. The ideal device for pediatric mechanical
circulatory support should be capable of providing support
across a large range of patient sizes—from newborns to
young adults. Existing paracorporeal systems require major
skin penetrations, which commonly result in substantial risk
for infection. Beyond implications for the pump itself,
however, size considerations exist for all aspects of device
design for children including cannulas, energy sources, and
control mechanisms. In addition to challenges relating to the
size of the pediatric patient, the diverse anatomic variations
routinely encountered in congenital heart disease make
universal application of a single pump design impossible.
Specifically, abnormalities of the systemic and pulmonary
venous anatomy affect design of pump inflow while
abnormalities of the great arteries impact on the design of
pump outflow. Abnormalities of visceroatrial situs, such as
situs inversus, and abnormalities of the location of the
cardiac apex, such as dextrocardia and heterotaxy, may
make institution of support difficult for many existing pump
designs.
Circulatory support devices for children should take into
account other physiologic considerations unique to pediat-
rics. Children, especially newborns, are more prone to
complications related to anticoagulation and are vulnerable
to the infections commonly associated with mechanical
circulatory support [15]. Newborns often manifest an
exaggerated systemic inflammatory response after cardio-
pulmonary bypass that may evolve into multi-system organ
failure during prolonged ECMO or VAD support. Also, a
large percentage of children who require a VAD need urgent
institution of support to treat cardiac arrest following cardiac
surgery or in the setting of acute myocarditis [15,25–27]. To
address these issues, pediatric circulatory support devices
should require only minimal or no anticoagulation, mini-
mize the risk of infection, trauma to blood elements, and
systemic inflammation, and allow rapid deployment to
improve outcomes [25,28,29].
Despite these challenges, mechanical circulatory support
has become an important option for treatment of pediatric
cardiac disease. In the acute setting, even the most severe
cases of postcardiotomy circulatory failure and various
medical conditions such as myocarditis and cardiomyopathy
can be managed with mechanical circulatory support if
medical management fails [15–18,22–56]. For isolated
postcardiotomy failure, the availability of mechanical
circulatory support has often provided the ‘‘safety net’’ that
has allowed increasingly complex surgical procedures to be
developed for children with the most severe forms of
congenital heart disease. In addition to the use of
mechanical circulatory support in the acute setting, there
exists an expanding patient population with congenital heart
disease that may benefit from chronic mechanical circula-
tory support. One such important patient category to be
discussed below includes children who possess single
ventricle physiology who have undergone the series of
palliative operations referred to as the ‘‘Fontan pathway’’
that physiologically septates the pulmonary and systemic
circulations. The great majority of children are now
surviving after the Fontan procedure who would have
otherwise died during childhood. Having survived through
childhood, but possessing palliated circulatory physiology,
many of these patients may develop the need for implant-
able circulatory support devices as a bridge to transplanta-
tion or as destination therapy in the future.
2.2. Mechanical support of the failing single ventricle
Due to increasingly successful early management, the
population of patients with palliated single ventricle
physiology who develop failure of the systemic ventricle
will undoubtedly continue to increase. The need for
mechanical circulatory support for this patient population
is expected to increase in parallel as a bridge to
transplantation and perhaps eventually as destination
therapy. There are a limited number of reports describing
the use of ECMO and VADs primarily for short-term
circulatory support for these patients, while very little
experience exists for chronic support of the failing single
ventricle [19,57,58]. This will be a particularly challenging
patient population to support with a number of unique
issues. For example, these patients often exhibit anatomic
abnormalities of the great arteries and veins, which may
make cannulation difficult. Most of these patients encoun-
tered beyond early childhood have undergone multiple
operations predisposing them to complications that occur
in any reoperative cardiac surgical patient. Finally, many
of these patients suffer from complications resulting from
venous hypertension in the splanchnic circulation such as
cirrhosis, ascites and protein losing enteropathy. Therefore,
many of these patients will have ongoing issues related to
infection, malnutrition and postoperative bleeding at the
time of device implantation, or be predisposed to their
development postoperatively.
Perhaps the greatest challenge will be to understand and
appropriately manage the underlying physiology of patients
with single ventricles while supported using devices
designed for patients with two ventricles. In the vast
majority of cases, effective support of failing Fontan
circulation can be achieved with apical cannulation of the
systemic ventricle for drainage with reinfusion via the aorta
as is performed for left ventricular assistance in two
ventricle physiology. Left-sided support would reduce the
filling pressure of the single ventricle, which would result in
decreased pressure in the Fontan (pulmonary) circuit. This
would undoubtedly provide substantial reduction in system-
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184 175
ic venous hypertension thereby improving pulmonary and
systemic hemodynamics with assistance of the left-side
circulation alone.
Significant improvement would be expected even in
cases where complications of systemic hypertension in the
splanchnic circulation predominate, such as isolated protein
losing enteropathy. Placing a pump directly in the Fontan
pathway would probably usually be less useful and would
provide a number of additional challenges. This approach
would be limited to settings in which pulmonary vascular
resistance was elevated due to recurrent pulmonary emboli
or pulmonary parenchymal disease, with preserved single
ventricle function. Even in these cases great care in
management would be required if, for example, a single
axial flow pump was placed in the inferior vena cava limb of
the Fontan circuit to avoid dangerous elevations of systemic
venous pressure in the superior vena cava and remainder of
the pulmonary circuit. In addition, increased filling of the
systemic ventricle due to increased pulmonary flow might
unmask subclinical dysfunction of the single ventricle.
Regardless of the side of the circulation supported,
mechanical support instituted for systemic venous hyper-
tension due to a failing single ventricle might be able to be
effectively achieved with relatively low flows and minimal
energy requirements. Perhaps only intermittent use would
be required. For example, support applied only during sleep
might effectively reverse complications related to systemic
venous hypertension if regurgitation through the device was
limited during periods when device flow was not occurring.
The exact details of mechanical circulatory support systems
for the failing Fontan circulation remain largely speculative
at the moment, but represent another potentially exciting
application of mechanical circulatory support of congenital
heart disease.
3. Special topics in pediatric mechanical circulatory
support
3.1. Use of rapid resuscitation ECMO in the treatment of
cardiorespiratory arrest
Cardiac arrest is a common indication for ECMO,
accounting for nearly 25% of all indications for mechan-
ical circulatory support of pediatric patients [15]. Several
groups have developed systems that allow the expeditious
institution of ECMO after cardiac arrest that is refractory
to conventional cardiopulmonary resuscitation [25,28,29].
One system that has been described utilizes a modified
ECMO circuit, an organized team of personnel to perform
cannulation, and a streamlined priming process [25]. The
‘‘rapid resuscitation’’ ECMO circuit is maintained vacuum
and CO2-primed in the intensive care unit and is portable
with a battery power supply allowing it to be quickly
utilized in any location throughout the hospital. If standard
CPR is unsuccessful within 10 min, the circuit is moved to
the patient’s bedside and crystalloid priming is initiated
while cannulation is proceeding. If cannulation is com-
pleted prior to the availability of blood products, ECMO
flow is initiated with a crystalloid-primed circuit and blood
products are added when available. In the original
description of this system, 11 pediatric cardiac patients
who had suffered cardiorespiratory arrest were resuscitated
with this rapid resuscitation approach [25]. The median
duration of CPR for these 11 patients was 55 min (range
15–103 min) compared to a median duration of CPR of 90
min (range 45–200 min) for seven historical controls
resuscitated with conventional means prior to the utiliza-
tion of the rapid resuscitation system. All but one of the 11
rapid resuscitation patients were weaned from ECMO with
seven patients (64%) surviving to hospital discharge
compared to two survivors (29%) of the seven historical
controls.
Jacobs and coworkers reported a rapid resuscitation
system based on a circuit that employs a hollow-fiber
oxygenator and a centrifugal pump [29]. This system is fully
portable with a priming volume of 250 ml and is heparin-
bonded throughout. The use of the centrifugal pump
eliminates the need for gravity drainage, which results in
shorter tubing lengths and greater portability. A major
advantage of this system is the extremely short set-up time
which enables crystalloid priming to be completed in as
little as 5 min. Using this system, the duration of CPR was
only 12 min prior to the institution of ECMO.
These reports support the concept that pediatric cardiac
patients who suffer cardiac arrest often deserve an aggres-
sive approach with prompt institution of ECMO if
conventional resuscitative measures fail. Rapid institution
of circulatory support with modified ECMO systems can be
life saving with preservation of end-organ function in these
patients.
3.2. Support for hypoplastic left heart syndrome and other
single ventricle forms
In a report of a single center’s pediatric mechanical
circulatory support experience through 1996, only 2% of all
cases were children with hypoplastic left heart syndrome
[15]. A subsequent report from 2001 demonstrated that
perioperative support of the Norwood procedure was the
single largest diagnostic category (28%) for all pediatric
cardiac cases who required circulatory support [59]. This
difference over a 5-year period is representative of trends
reported by other institutions. While previously considered
to be a relative contraindication, patients who possess
hypoplastic left heart syndrome and other forms of single
ventricle physiology are now considered to be candidates
for mechanical circulatory support. In fact, several reports
have emphasized the importance of having an active ECMO
program available at pediatric cardiac centers to provide the
full complement of treatment options for these complex
patients [57,59,60].
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184176
Pizarro and Aharon described survival rates of 50% and
64%, respectively, for infants who required mechanical
circulatory support after the Norwood procedure [59,60].
While conventional ECMO may be used in these patients,
Darling and co-authors reported 80% survival utilizing a
circuit configured without an oxygenator to support patients
after the Norwood procedure [57].
3.3. Mechanical circulatory support for acute, fulminant
myocarditis
The survival rate for children who require mechanical
circulatory support for myocarditis is relatively good in
most reports [33,34,61–65]. A recent multi-institutional
review of 15 patients with viral myocarditis supported by
ECMO (12 patients) or VADs (3 patients) demonstrated an
overall survival rate of 80% [27]. Nine of 15 patients were
weaned from support with seven survivors (78%) while the
remaining six patients were successfully bridged to
transplantation with five survivors (83%). An especially
important finding was that all non-transplanted survivors
are currently alive with normal ventricular function. Two
recent reports further emphasize the likelihood of recovery
in these patients with survival rates of 73% and 100%; no
patient in either series required transplantation and all
survivors demonstrated normal ventricular function
[66,67]. Historically, it was believed that a significant
percentage of children with acute myocarditis would
develop dilated cardiomyopathy with the ultimate need
for cardiac transplantation. These studies suggest that
children with acute, fulminant myocarditis have an overall
favorable outcome and a significant degree of disease
reversibility if successfully supported during the acute
phase of illness.
The reasons for better long-term outcomes and a
decreased incidence of progression to dilated cardiomyop-
athy in patients most severely affected by myocarditis
remains unexplained. However, mechanical circulatory
support may contribute to the improved long-term outcomes
in these children. It is reasonable to speculate that
normalization of ventricular geometry and function by the
early institution of support may help to prevent progression
to dilated cardiomyopathy.
Based on these results, the optimal approach for children
presenting with acute fulminant myocarditis may be to
provide mechanical circulatory support, even if required for
prolonged periods, in anticipation of eventual ventricular
recovery. Previous reports have demonstrated the feasibility
of this approach with full return of ventricular function in
children and young adults with myocarditis after weeks or
months of mechanical support [23,54,68,69]. Prolonged
mechanical circulatory support in a larger number of
pediatric patients with fulminant myocarditis may reveal
that extended MCS in children restores native ventricular
function, thereby obviating the need for transplantation in
virtually all of these children.
4. Existing pediatric circulatory support devices
The circulatory support devices currently available for
clinical use to support the circulation in pediatric patients
are described below.
4.1. ECMO
Reports of single center’s experience usually find that
conditions of complex cyanotic heart disease with either
excess pulmonary blood flow (such as transposition of the
great arteries) or decreased pulmonary blood flow (such as
tetralogy of Fallot) constitute the majority of cases requiring
ECMO for pediatric cardiac support [15,49,70]. The most
common scenarios for support usually occur in children
after cardiac surgery, namely, failure to wean from
cardiopulmonary bypass and cardiogenic shock or cardiac
arrest occurring in the intensive care unit postoperatively
[33,38,45,48,50,51,55,70–75]. However, refractory medical
conditions also occur in children that require mechanical
circulatory support including hypoxia and pulmonary
hypertension, along with diseases of the myocardium
including metabolic cardiomyopathy and myocarditis
[24,27,34,54,76,77]. Conditions that were historically felt
to represent contraindications for ECMO are now often
successfully supported. For example, patients with shunted
single ventricle physiology, including patients with hypo-
plastic left heart syndrome, were often denied ECMO in the
past due to difficulties in achieving balance between the
pulmonary and systemic circulations during support. Due to
improvements in management, ECMO and VADs are
currently felt to be necessary adjuncts to the successful
surgical approach to these patients [15,55,57,60,70,78].
Since its inception, ECMO has served as the predominant
form of support for children. Due to the presence of an
oxygenator in the circuit, ECMO is most useful in providing
support when heart disease is accompanied by hypoxia and
pulmonary hypertension. ECMO is also capable of provid-
ing bi-ventricular support and may be instituted via
cannulation of peripheral vessels. However, much of the
predominance of ECMO in pediatric mechanical circulatory
support is due simply to device availability and familiarity;
pediatric centers have historically greater experience with
ECMO due to its widespread use in the treatment of
pediatric respiratory failure. However, due to the complexity
of the ECMO circuit, substantial morbidity, if not mortality,
is incurred with this type of support compared to the
relatively simpler VAD circuit. In the acute setting,
increased tubing lengths and the presence of an oxygenator
damage blood elements and increase activation of the
inflammatory cascade [15–18,23,24,29,41,54]. The pres-
ence of an oxygenator and other complexities of the ECMO
circuit such as the ‘‘bladder box’’ require higher levels of
anticoagulation, which makes hemorrhagic complications
more common especially when support is required in the
immediate postoperative period. In a recent report, in-
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184 177
hospital neurologic complications due to both intracranial
hemorrhage and embolic events were three times more
likely in children supported with ECMO compared with
those supported with VADs [15,17,41]. Neurologic morbid-
ity persisted in these children with significantly more
ECMO supported children demonstrating neurologic im-
pairment during long-term follow-up [13,14].
Another important difference between devices is the
impact on recovery of ventricular function during support.
Experimental studies have demonstrated increased ventric-
ular wall stress during ECMO support while VADs provide
better ventricular unloading leading to decreased wall stress
[79,80]. ECMO may also contribute to ongoing myocardial
damage during support by providing desaturated blood flow
to the coronary arteries. With most cannula configurations
employed for venoarterial ECMO, oxygenated blood from
the arterial cannula fails to reach the coronary arteries with
coronary arterial blood flow provided by the left ventricle
only if there is any appreciable ventricular ejection [81–83].
If there is significant pulmonary parenchymal disease or
mechanical ventilation is withheld during ECMO support,
hypoxic blood returning to the left ventricle may provide the
sole source of coronary perfusion with deleterious effects on
ventricular function and recovery [84]. Desaturated coro-
nary artery blood flow may go unnoticed because peripheral
arterial blood gases will be fully saturated and may not
reflect the oxygen level in the aortic root. Finally, and
perhaps most importantly, ECMO provides only short-term
support, requires intensive nursing management, and is not
suitable for ambulatory support. ECMO support is invari-
ably limited to days to a few weeks; after this time period,
multi-system organ failure invariably ensues, probably due
to chronic activation of the inflammatory cascade that
occurs during ECMO support [15,18,19,41].
4.2. Centrifugal pump VAD
Centrifugal pump systems, such as the Bio-Pump
(Medtronic Bio-Medicus, Minneapolis, MN), are the most
commonly used form of VAD support for children. Such
VADs provide non-pulsatile flow by a constrained vortex
design that is both pre-load and after-load sensitive. The
centrifugal VAD circuit employs short tubing lengths to
connect the pump to the venous and aortic cannulas, which
reduces priming volumes compared to ECMO and makes
the system easy to maintain [15,29,85]. Heparin require-
ments as well as trauma to blood elements may be reduced
with Bio-Pump-based VAD circuits owing to the absence of
an oxygenator or venous reservoir. Despite its simplicity and
proven track record, the chief limitation for the Bio-Pump
VAD, like ECMO, is its unsuitability for prolonged support.
Thuys reported excellent results using the Bio-Pump to
support infants and children weighing 6 kg or less [86].
Utilizing this system, the authors supported 34 children with
median age of 60 days (range 2–258 days) and weight of
3.7 kg (range 1.9–5.98 kg). Of 34 supported, 63% were
successfully weaned from VAD support and 31% of this
difficult patient population survived to hospital discharge.
Other reports have described the utility of centrifugal VAD
to support the entire spectrum of pediatric cardiac disease
[31,42,46,47,87–89].
4.3. Adult systems used for pediatric support-Heartmate,
Thoratec and the ABIOMED BVS 5000
Several groups have successfully provided mechanical
circulatory support for older children utilizing systems
designed primarily for adult applications [31,44,90,91].
Helman described the use of the Heartmate VAD (Thoratec
Corp., Pleasanton, CA) in 12 adolescent patients, the
majority of whom had idiopathic dilated cardiomyopathy
[44]. The relatively older age of these patients (range 11–20
years) and larger size (body surface area range 1.4–2.2 m2)
allowed the use of this device. As in the adult experience,
the majority of children supported by the vented electric
model were discharged home with resumption of normal
activities.
A number of reports exist describing experience with the
Thoratec VAD (Thoratec Corp., Pleasanton, CA) in children
[90–93]. In Reinhartz’s review, 101 pediatric patients
[median age 13.7 years (range 7–17 years), median weight
54 kg (17–110 kg), median body surface area 1.5 m2 (range
0.7–2.2 m2)] had undergone support with the Thoratec VAD
worldwide with 66% survival to hospital discharge [93].
Ashton and co-workers employed the ABIOMED BVS
5000 (ABIOMED, Inc., Danvers, MA) in four older
children [31]. The ABIOMED device was used to provide
temporary circulatory support for patients with a body
surface area greater than 1.2 m2 with flows greater than 2 L/
min. A particular limitation to more widespread pediatric
application of devices designed primarily for adults can be
attributed to low pump rates during support for all but the
largest children limiting pump wash-out leading to increased
thromboembolic risk [22,31].
4.4. Pulsatile pediatric VADs-MEDOS HIA VAD and the
Berlin Heart
The MEDOS HIA VAD (MEDOS Medizintechnik AG,
Stolberg, Germany) and the Berlin Heart VAD (Berlin Heart
AG, Berlin, Germany) are paracorporeal pulsatile VAD
systems. Because the systems are available in a variety of
pump sizes (10–80 ml), they are suitable for the entire age
range of pediatric patients including neonates [21,94]. Both
are paracorporeal systems that employ pneumatically
driven, flexible blood sac pumps, to provide pulsatile flow.
Inlet and outlet valves are tri-leaflet and constructed from
polyurethane in the smallest versions.
Both the MEDOS and Berlin Heart systems are superior
to ECMO in providing moderate to long-term support and
preserve the options of bridging to transplantation or
recovery for children. Also unlike ECMO, both of these
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184178
systems allow extubation and ambulation during support
with the same salutary effects provided by similar systems
designed for adults. Several series have been published
describing use of the MEDOS system for pediatric support
[20,23,61,93]. Reinhartz reported 64 children supported
with the MEDOS HIAVAD, 44% of whom were supported
with the smallest pump sizes with an overall survival of
38% for patients with available follow-up [93]. A number of
reports exist detailing results with the Berlin Heart VAD in
children [21,22,24,53,54,95–98]. The Berlin Heart VAD
appears to have fewer bleeding complications compared to
ECMO with decreased blood product utilization during
support [97]. A recent report noted improving results for
infant support in the latest cohort of patients with survival
rates now approaching those achieved in adults [98]. The
worldwide experience with the Berlin Heart VAD in
pediatric patients now exceeds one hundred patients (Dr.
Peter Goettel, Berlin Heart AG, Berlin, Germany, personal
communication). In the United States, because device
availability is restricted to emergency use, only 25 implants
have been performed.
4.5. The MicroMed DeBakey VAD child
The DeBakey VAD Child (MicroMed Technology, Inc.,
Houston, TX) was granted Humanitarian Device Exemption
(HDE) status by the Food and Drug Administration and
became available for use in 2004 [99]. This pediatric device
employs the same axial-flow pump used in the adult version
with design modifications aimed at reducing the lateral
space requirements for device implantation. These design
modifications include a shortened inflow cannula with a
more acute angle for the inflow tubing, a shortened plastic
outflow graft protector and reduced size of the flow probe
on the outflow graft. Under the current HDE, the VAD Child
is used to provide temporary left ventricular support as a
bridge to cardiac transplantation for children from 5 to 16
years of age with a BSA >0.7 m2 and <1.5 m2 and is
designed to be fully implantable in this size range.
Although the clinical experience is still limited, this
device has been used successfully in a number of children
since its introduction.
5. Pediatric circulatory support devices under
development
The clear need for better means to chronically support the
circulation in infants and children with congenital and
acquired heart disease resulting in severe heart failure has
stimulated recent efforts to develop these much needed
devices. The development of these devices is being funded
by government agencies, industry, and institutions. The
National Heart, Lung, and Blood Institute currently supports
the development of pediatric circulatory support devices
through its Pediatric Circulatory Support Contract Program
and various grants. The program and the devices being
developed through NHLBI support are described below.
Other devices under development intended specifically for
pediatric circulatory support are also described.
5.1. NHLBI pediatric circulatory support program
On March 30, 2004, five 5-year contracts totaling
$22,399,727 were awarded by the NHLBI to provide a
comprehensive program for the development of a family of
novel pediatric circulatory support devices. The types of
devices intended to be developed under the program
included left and right VADs, ECMO systems, and other
novel bioengineered systems for children ranging in weight
from 2 to 25 kg. The devices funded by the program are
described below.
5.1.1. The PediaFlow (University of Pittsburgh; Carnegie
Mellon University; Children’s Hospital of Pittsburgh;
LaunchPoint, LLC; and World Heart Corporation)
The PediaFlow VAD is an implantable, magnetically
suspended mixed-flow turbodynamic blood pump being
developed to provide up to 6 months of circulatory support
to patients from 3 to 15 kg in body weight who have
congenital or acquired heart disease. Anticoagulation
therapy while on the device is intended to be limited to
anti-platelet medications. The targeted flow rate range of the
devices is from 0.3 to 1.5 L/min. It is being designed to have
a maximum weight of 30 g, a maximum volume of 5 ml, a
maximum priming volume of 0.5 ml, and to require only a
single percutaneous lead for energy transmission. The
PediaFlow VAD’s ‘‘smart’’ sensor-based controller will
continuously monitor the performance of the PediaFlow
device and support either continuous or pulsatile flow
modes. The device’s cannulae will be designed to be
suitable for both left and right ventricle cannulation (NHLBI
Contract HHSN268200448192C).
5.1.2. pCAS (Ension, Inc.; University of Louisville; Seare
Biomatrix Systems; Fluent, Inc.)
The pediatric Cardiopulmonary Assist System, or
pCAS, is a compact, paracorporeal rotary flow device
capable of simultaneously pumping blood and providing
oxygenation. The device rotor is fabricated from layers of
microporous hollow fibers through which gas exchange
occurs. These fibers will have a custom coating to both
increase fiber life and minimize requirements for systemic
anticoagulation.
The paracorporeal design of the pCAS system affords
modularity, allowing a separate device for each target
patient population, and the possibility of device exchange
during the support period. Such modularity also permits
the patient to be ‘‘upgraded’’ from the neonatal-sized
device to the child-sized device as growth or support needs
change. In addition to steady flow, the pCAS system will
include an option to deliver pulsatile flow at the higher
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184 179
heart rates of the intended patient population. (NHLBI
Contract HHSN268200448189C).
5.1.3. Infant- and Child-size Jarvik 2000 (Jarvik Heart,
Inc.; University of Maryland Medical Center; Mississippi
State University; Whalen Biomedical, Inc.)
Jarvik Heart is developing child- and infant-sized versions
of the Jarvik 2000\ that will provide full or partial circulatory
support for more than 6 months. The 35 g, 10 ml child-size
model is intended for 15–25 kg children and the 12 g, 4 ml
infant-size model is intended for 3–15 kg children. Through
device design and using various creative surgical techniques,
these small pediatric Jarvik 2000 models should be implant-
able in any of the normal heart’s four chambers in order to
provide chronic mechanical left, right, or biventricular
support (NHLBI Contract HHSN268200448190C).
5.1.4. Penn State PVADs (Penn State University;
Minnetronix, Inc.)
The Penn State Pediatric Ventricular Assist Device
(PVAD), is a pulsatile, pneumatically actuated blood pump
based on the design principles of the adult-sized Pierce–
Donachy VAD. The device is intended to be used for left,
right, or biventricular support for up to 6 months and is
being developed in two sizes. The smaller infant-size device
has a 12 ml dynamic stroke volume size for infants ranging
in weight from 5 to 15 kg. The larger child-size device has a
25 ml stroke volume size for children 15–35 kg. The target
flow rate ranges of the infant and child-size devices are 0.5–
1.3 and 1.3–3.3 L/min, respectively. The device is intended
primarily for paracorporeal placement but will also be
implantable for bridge-to-transplant applications (NHLBI
Contract HHSN268200448191C).
Fig. 1. The intravascular PediPump deployed as a BVAD (A) and the extravascu
Cleveland Clinic Foundation, 2005, used with permission.
5.1.5. PediPump (The Children’s Hospital at the Cleveland
Clinic; The Department of Biomedical Engineering, The
Cleveland Clinic Foundation; Foster-Miller Technologies,
Inc.)
The PediPump is a mixed-flow VAD with a rotating
assembly consisting of an impeller in the front, front and rear
radial magnetic bearings and a motor rotor magnet in its
center. Blood enters axially at the inlet and is turned to exit the
pump at an intermediate angle through the pump’s outside
diameter. Titanium shells seal all potentially corrodible
components from blood and tissue. The initial PediPump
prototype measures approximately 7�75 mmwith a priming
volume of 0.6 ml, imparting less than 10% of the physical
displacement of currently available axial flow pumps.
The PediPump’s deployment will be based on patient
size: for larger children (>15 kg), the small size of the
PediPump may allow completely intravascular implantation
(Fig. 1A). For smaller children (<15 kg), extravascular,
intracorporeal implantation may be performed using stan-
dard cannulation strategies employed for existing axial flow
pumps with inflow and outlet cannulas configured as needed
(Fig. 1). The same basic pump is anticipated for use as a
right ventricular assist device (RVAD), left ventricular assist
device (LVAD), or a biventricular assist device. (NHLBI
Contract HHSN268200448188C).
5.2. Other NHLBI-supported research
5.2.1. Pediatric pVAD (CardiacAssist)
CardiacAssist, Inc., is assessing the feasibility of
modifying its TandemHeart\ PTVA\ (Percutaneous Trans-
septal Ventricular Assist) System, developed for adults, for
pediatric patients. The device, which will be placed on the
lar, intracorporeal PediPump deployed as a BVAD (B). Copyright by The
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184180
outside of the body, is expected to deliver up to 50% of the
normal cardiac output in infants and children with heart
disease or heart defects. To accommodate pediatric patients
who weigh between 3.5 and 50 kg, six different cannulas are
planned for development (Supported by Grant R44
HL078077).
5.2.2. CardioFlowPQ (Ension)
Ension is developing the CardioFlow PQ blood pump
system to provide pulsatile flows in neonatal and pediatric
patients. The device, which is based on the porous pump
rotor concept being used in the pCAS devices described
previously, is being designed to more effectively entrain
blood to generate effective pulse pressures at the requisite
high beat-rates than other commercially available pulsatile
pumps. (Supported by Grant R44 HL059810).
5.2.3. Miniature MagLev VAD (Levitronix)
Levitronix is currently developing two pediatric devices,
the Levitronix Short-Term and Long-Term Pediatric VADs,
based on bearingless motor technology. The Short-Term
Pediatric VAD (Fig. 2A) is intended to provide circulatory
support for up to 14 days. The system includes a
polycarbonate pump with a 14 ml priming volume capable
of generating up to 3.0 LPM flow at a speed of 5500 rpm
against a pressure drop of 300 mm Hg. Actuation is
accomplished by magnetically levitating and rotating a
freely suspended impeller. The Long-Term pediatric VAD
(Fig. 2B) is based on the same bearingless motor technol-
ogy. The system includes a titanium pump with a 7.5 ml
priming volume capable of generating up to 6.0 LPM flow
at a speed of 9000 rpm against a pressure drop of 200 mm
© 2005 Levitronix LLC
© 2005 Levitronix LLC
© 2005 Levitronix LLC
A
B
Fig. 2. The Levitronix pediatric short-term pump (A) and long-term pump
and motor (B). Copyright by Levitronix LLC, 2005, used with permission.
Hg. The intended duration of use is for up to 6 months
(Supported by Grant R44 HL074628).
5.2.4. Toddler VAD (Pittsburgh/Carnegie-Mellon
University)
The overall goal of this project is to develop a safe,
reliable, and biocompatible VAD for toddlers/small children
between 15 and 35 kg. The ‘‘Toddler VAD’’ (TVAD), shown
in Fig. 3, will utilize a mixed-flow pump design with hybrid
magnetic and blood-lubricated bearings, optimized to
minimize blood trauma and thrombosis. The device will be
fully implantable, and capable of providing extended support
for up to 3 months (Supported by Grant R41 HL077028).
5.2.5. Fetal Perfusion System (Ension, Inc.)
Approximately 0.8% of children are born with congenital
heart defects that are detectable within the first trimester. If
these defects could be corrected in utero, outcomes may be
improved by eliminating the need for multiple, complex
surgeries after birth. In response, Ension has begun
development of a fetal cardiac bypass circuit enabling
correction of certain congenital heart defects before birth
(Fig. 4). The circuit consists of a specialized miniature
centrifugal pump and a miniature oxygenator—both specif-
ically designed for the unique aspects of fetal bypass. This
modular system will have an ultra-low priming volume and
will provide pulsatile flow and gas transfer, if required
(Supported by Grant R43 HL079737).
5.3. Other devices
The Circulite Micro-VAD (Aachen, Germany) is a small
implantable axial flow VAD designed to produce flows up
to 3 LPM. The device, which has blood immersed hybrid
bearings, a priming volume of 1.5 ml, a diameter of 12 mm,
and a length of 50 mm. No signs of hemolysis or emboli
were found following short-term (four weeks) animal
studies of the device. Longer-term animal studies are being
planned to further demonstrate safety [100].
A miniature centrifugal rotary VAD known as the
TinyPump is being developed in Japan by investigators at
Tokyo Medical and Dental University, Okayama University
in Okayama, and Ekisaikai Hospital in Nogoya [101]. The
device has a height of 20 mm, a diameter of 49 mm, and a
priming volume of 5 ml. In vitro tests reveal that the device
can generate up to 4 LPM and an index of hemolysis similar
to that of the Bio-Pump. Successful acute animal studies of
the device have been completed and efforts are continuing
to assess the pump_s performance at low flow rates in
chronic animal studies.
6. Future directions and summary
Each of the pediatric devices under development targets
features to address the needs of pediatric patients needing
Fig. 3. The Toddler VAD shown with a cut-away view of the mixed-flow pump. Copyright by Carnegie Mellon University, 2005, and University of Pittsburgh,
2004, used with permission.
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184 181
circulatory support, such as size, expected duration of support,
intention of therapy as a bridge or to aid recovery, and type of
heart disease. Together, these devices are expected to help
provide the missing options for the vulnerable, small pediatric
patients who are currently limited to short-term extracorporeal
VADs and cumbersome conventional ECMO. However,
substantial work must be completed before these devices are
ready for clinical use.Clinical evaluations for the devices being
developed under the NHLBI Pediatric Circulatory Support
Program are expected to begin at or before the conclusion of
Fig. 4. The ension fetal perfusion system.
the development program in 2009. The other devices under
development are expected to be ready for clinical use at various
times with the earliest expected to be ready for clinical trials
within a few years.
Acknowledgements
The authors would like to thank James Antaki, Ph.D.
(Carnegie Mellon University), Mark Gartner (Ension, Inc.),
Kurt Dasse, Ph.D. (Levitronix, Inc.), and David Wang, Ph.D.
(CardiacAssist, Inc.) for their contributions and Tracey Hoke,
M.D., Sc.M. (NHLBI) for her contributions as co-Project
Officer for NHLBI’s Pediatric Circulatory Support Program.
Conflicts of Interest: Dr. Baldwin is an employee of NHLBI
and a Project Officer for NHLBI’s Pediatric Circulatory
Support Program and administrator for numerous grants to
develop pediatric circulatory support devices. Dr. Duncan is
the PI for the contract awarded to The Cleveland Clinic and is
a member of the Advisory Board for the DeBakey VAD
Child, a product of MicroMed Technologies, Inc.
References
[1] McBride LR, Naunheim KS, Fiore AC, et al. Risk analysis in patients
bridged to transplantation. Ann Thorac Surg 2001;71:1839–44.
[2] Navia JL, McCarthy PM, Hoercher KJ, Smedira NG, Banbury MK,
Blackstone EH. Do left ventricular assist device (LVAD) bridge-to-
transplantation outcomes predict the results of permanent LVAD
implantation? Ann Thorac Surg 2002;74:2051–62 [discussion
2062–3].
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184182
[3] Korfer R, El-Banayosy A, Arusoglu L, et al. Single-center experience
with the Thoratec ventricular assist device. J Thorac Cardiovasc Surg
2000;119:596–600.
[4] Farrar DJ, Hill JD. Univentricular and biventricular Thoratec VAD
support as a bridge to transplantation. Ann Thorac Surg
1993;55:276–82.
[5] Pennington DG, McBride LR, Peigh PS, Miller LW, Swartz MT.
Eight years’ experience with bridging to cardiac transplantation. J
Thorac Cardiovasc Surg 1994;107:472–80 [discussion 480–1].
[6] Frazier OH, Rose EA, McCarthy P, et al. Improved mortality and
rehabilitation of transplant candidates treated with a long-term
implantable left ventricular assist system. Ann Surg 1995;222:327–
36 [discussion 336–8].
[7] McCarthy PM. HeartMate implantable left ventricular assist device:
bridge to transplantation and future applications. Ann Thorac Surg
1995;59:S46.
[8] Rose EA, Moskowitz AJ, Packer M, et al. The REMATCH trial:
rationale, design, and end points. Randomized Evaluation of
Mechanical Assistance for the Treatment of Congestive Heart
Failure. Ann Thorac Surg 1999;67:723–30.
[9] Boehmer JP. Device therapy for heart failure. Am J Cardiol
2003;91:53D–9D.
[10] Rose EA, Gelijns AC, Moskowitz AJ, et al. Long-term mechanical
left ventricular assistance for end-stage heart failure. [comment][-
summary for patients in J Card Fail. 2002 Apr;8 (2) 59–60; PMID:
12016626]N Eng J Med 2001;345:1435–43.
[11] Pasque MK, Rogers JG. Adverse events in the use of HeartMate
vented electric and Novacor left ventricular assist devices: comparing
apples and oranges. J Thorac Cardiovasc Surg 2002;124:1063–7.
[12] Kukuy EL, Oz MC, Rose EA, Naka Y. Devices as destination
therapy. Cardiol Clin 2003;21:67–73.
[13] Ibrahim AE, Duncan BW, Blume ED, Jonas RA. Long-term follow-
up of pediatric cardiac patients requiring mechanical circulatory
support. Ann Thorac Surg 2000;69:186–92.
[14] Ibrahim AE, Duncan BW. Long-term follow-up of children with
cardiac disease requiring mechanical circulatory support. In: Duncan
WB, editor. Mechanical circulatory support for cardiac and respira-
tory failure in pediatric cardiac patients. New York’ Marcel Dekker,
Inc., 2001. p. 205–20.
[15] Duncan BW, Hraska V, Jonas RA, et al. Mechanical circulatory
support in children with cardiac disease. J Thorac Cardiovasc Surg
1999;117:529–42.
[16] Duncan BW. Mechanical circulatory support in infants and children
with cardiac disease. In: Zwischenberger JB, Bartlett RH, editors.
ECMO extracorporeal cardiopulmonary support in critical care. Ann
Arbor’ Extracorporeal Life Support Organization, 2000.
[17] Duncan BW. Extracorporeal membrane oxygenation for children
with cardiac disease. In: Duncan BW, editor. Mechanical circulatory
support for cardiac and respiratory failure in pediatric cardiac
patients. New York’ Marcel Dekker, Inc., 2001. p. 1–20.
[18] Duncan BW. Mechanical circulatory support for cardiac and
respiratory failure in pediatric cardiac patients. New York’ Marcel
Dekker, Inc.; 2001.
[19] Duncan BW. Mechanical circulatory support for infants and children
with cardiac disease. Ann Thorac Surg 2002;73:1670–7.
[20] Sidiropoulos A, Hotz H, Konertz W. Pediatric circulatory support. J
Heart Lung Transplant 1998;17:1172–6.
[21] Hetzer R, Hennig E, Schiessler A, Friedel N, Warnecke H, Adt M.
Mechanical circulatory support and heart transplantation. J Heart
Lung Transplant 1992;11:175–81.
[22] Ishino K, Loebe M, Uhlemann F, Weng Y, Hennig E, Hetzer R.
Circulatory support with paracorporeal pneumatic ventricular assist
device (VAD) in infants and children. Eur J Cardiothorac Surg
1997;11:965–72.
[23] Konertz W, Hotz H, Schneider M, Redlin M, Reul H. Clinical
experience with the MEDOS HIA–VAD system in infants and
children. Ann Thorac Surg 1997;63:1138–44.
[24] Hetzer R, Loebe M, Potapov EV, et al. Circulatory support with
pneumatic paracorporeal ventricular assist device in infants and
children. Ann Thorac Surg 1998;66:1498–506.
[25] Duncan BW, Ibrahim AE, Hraska V, et al. Use of rapid-deployment
extracorporeal membrane oxygenation for the resuscitation of
pediatric patients with heart disease after cardiac arrest. J Thorac
Cardiovasc Surg 1998;116:305–11.
[26] Duncan BW. Use of rapid deployment extracorporeal membrane
oxygenation for the resuscitation of children with cardiac disease
after cardiac arrest. In: Duncan BW, editor. Mechanical circulatory
support for cardiac and respiratory failure in pediatric cardiac
patients. New York’ Marcel Dekker, 2001. p. 169–82.
[27] Duncan BW, Bohn DJ, Atz AM, French JW, Laussen PC, Wessel
DL. Mechanical circulatory support for the treatment of children with
acute fulminant myocarditis. J Thorac Cardiovasc Surg 2001;
122:440–8.
[28] del Nido PJ, Dalton HJ, Thompson AE, Siewers RD. Extracorporeal
membrane oxygenator rescue in children during cardiac arrest after
cardiac surgery. Circulation 1992;86(suppl II):II-300–4.
[29] Jacobs JP, Ojito JW, McConaghey TW, et al. Rapid cardiopulmonary
support for children with complex congenital heart disease. Ann
Thorac Surg 2000;70:742–50.
[30] Andrews AF, Nixon CA, Cilley RE, Roloff DW, Bartlett RH. One- to
three-year outcome for 14 neonatal survivors of extracorporeal
membrane oxygenation. Pediatrics 1986;78:692–8.
[31] Ashton RC, Oz MC, Michler RE, et al. Left ventricular assist device
options in pediatric patients. ASAIO J 1995;41:M277.
[32] Baffes TG, Fridman JL, Bicoff JP, Whitehill JL. Extracorporeal
circulation for support of palliative cardiac surgery in infants. Ann
Thorac Surg 1970;10:354–63.
[33] Black MD, Coles JG, Williams WG, et al. Determinants of success in
pediatric cardiac patients undergoing extracorporeal membrane
oxygenation. Ann Thorac Surg 1995;60:133–8.
[34] del Nido PJ, Armitage JM, Fricker FJ, et al. Extracorporeal
membrane oxygenation support as a bridge to pediatric heart
transplantation. Circulation 1994;90:II66–9.
[35] del Nido PJ. Extracorporeal membrane oxygenation for cardiac
support in children. Ann Thorac Surg 1996;61:336–9.
[36] del Nido PJ, Duncan BW, Mayer J, et al. Left ventricular assist
device improves survival in children with left ventricular
dysfunction after repair of anomalous origin of the left coronary
artery from the pulmonary artery. Ann Thorac Surg 1999;67:
169–72.
[37] Delius RE, Zwischenberger JB, Cilley R, et al. Prolonged extracor-
poreal life support of pediatric and adolescent cardiac transplant
patients. Ann Thorac Surg 1990;50:791–5.
[38] Delius RE, Bove EL, Meliones JN, et al. Use of extracorporeal life
support in patients with congenital heart disease. Crit Care Med
1992;20:1216–22.
[39] Dhillon R, Pearson GA, Firmin RK, Chan KC, Leanage R.
Extracorporeal membrane oxygenation and the treatment of critical
pulmonary hypertension in congenital heart disease. Eur J Cardio-
thorac Surg 1995;9:553–6.
[40] Doski JJ, Butler TJ, Louder DS, Dickey LA, Cheu HW. Outcome of
infants requiring cardiopulmonary resuscitation before extracorporeal
membrane oxygenation. J Pediatr Surg 1997;32:1318–21.
[41] Duncan BW. Extracorporeal membrane oxygenation versus ventric-
ular assist device support for children with cardiac disease. In:
Duncan BW, editor. Mechanical circulatory support for cardiac and
respiratory failure in pediatric cardiac patients. New York’ Marcel
Dekker, Inc., 2001. p. 61–74.
[42] Ferrazzi P, Glauber M, DiDomenico A, et al. Assisted circulation for
myocardial recovery after repair of congenital heart disease. Eur J
Cardiothorac Surg 1991;5:419–24.
[43] Galantowicz ME, Stolar CJH. Extracorporeal membrane oxygenation
for perioperative support in pediatric heart transplantation. J Thorac
Cardiovasc Surg 1991;102:148–52.
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184 183
[44] Helman DN, Addonizio LJ, Morales DLS, et al. Implantable left
ventricular assist devices can successfully bridge adolescent patients
to transplant. J Heart Lung Transplant 2000;19:121–6.
[45] Hunkeler NM, Canter CE, Donze A, Spray TL. Extracorporeal life
support in cyanotic congenital heart disease before cardiovascular
operation. Am J Cardiol 1992;69:790–3.
[46] Karl TR. Extracorporeal circulatory support in infants and children.
Semin Thorac Cardiovasc Surg 1994;6:154–60.
[47] Khan A, Gazzaniga AB. Mechanical circulatory assistance in
paediatric patients with cardiac failure. Cardiovasc Surg 1996;4:
43–9.
[48] Klein MD, Shaheen KW, Whittlesey GC, Pinsky WW, Arciniegas E.
Extracorporeal membrane oxygenation for the circulatory support of
children after repair of congenital heart disease. J Thorac Cardiovasc
Surg 1990;100:498–505.
[49] Meliones JN, Custer JR, Snedecor S, Moler FW, O’Rourke PP,
Delius RE. Extracorporeal life support for cardiac assist in pediatric
patients. Circulation 1991;84(suppl III):168–72.
[50] Raithel RC, Pennington DG, Boegner E, Fiore A, Weber TR.
Extracorporeal membrane oxygenation in children after cardiac
surgery. Circulation 1992;86(suppl II):II305–10.
[51] Rogers AJ, Trento A, Siewers RD, et al. Extracorporeal membrane
oxygenation for postcardiotomy cardiogenic shock in children. Ann
Thorac Surg 1989;47:903–6.
[52] Saito A, Miyamura H, Kanazawa H, Ohzeki H, Eguchi S.
Extracorporeal membrane oxygenation for severe heart failure after
Fontan operation. Ann Thorac Surg 1993;55:153–5.
[53] Schmitz C, Welz A, Dewald O, Kozlik-Feldmann R, Netz H,
Reichart B. Switch from a BIVAD to a LVAD in a boy with
Kawasaki disease. Ann Thorac Surg 2000;69:1270–1.
[54] Stiller B, Dahnert I, Weng Y, Hennig E, Hetzer R, Lange PE.
Children may survive severe myocarditis with prolonged use of
biventricular assist devices. Heart 1999;82:237–40.
[55] Ziomek S, Harrell JE, Fasules JW, et al. Extracorporeal membrane
oxygenation for cardiac failure after congenital heart operation. Ann
Thorac Surg 1992;54:861–8.
[56] Bartlett RH, Roloff DW, Custer JR, Younger JG, Hirschl RB.
Extracorporeal life support: the University of Michigan experience. J
Am Med Assoc 2000;283:904–8.
[57] Darling EM, Kaemmer D, Lawson DS, Jaggers JJ, Ungerleider RM.
Use of ECMO without the oxygenator to provide ventricular support
after Norwood Stage I procedures. Ann Thorac Surg 2001; 71:735–6.
[58] Kolovos NS, Bratton SL, Moler FW, et al. Outcome of pediatric
patients treated with extracorporeal life support after cardiac surgery.
Ann Thorac Surg 2003;76:1435–41 [discussion 144–2].
[59] Aharon AS, Drinkwater Jr DC, Churchwell KB, et al. Extracorporeal
membrane oxygenation in children after repair of congenital cardiac
lesions. Ann Thorac Surg 2001;72:2095–101 [discussion 210–2].
[60] Pizarro C, Davis DA, Healy RM, Kerins PJ, Norwood WI. Is there a
role for extracorporeal life support after stage I Norwood? Eur J
Cardiothorac Surg 2001;19:294–301.
[61] Martin J, Sarai K, Schindler M, Van de Loo A, Yoshitake M,
Beyersdorf F. Medos HIA-VAD biventricular assist device for bridge
to recovery in fulminant myocarditis. Ann Thorac Surg
1997;63:1145–6.
[62] Cofer BR, Warner BW, Stallion A, Ryckman FC. Extracorporeal
membrane oxygenation in the management of cardiac failure
secondary to myocarditis. J Pediatr Surg 1993;28:669–72.
[63] Frazier EA, Faulkner SC, Seib PM, Harrell JE, Van Devanter SH,
Fasules JW. Prolonged extracorporeal life support for bridging to
transplant. Perfusion 1997;12:93–8.
[64] Grundl PD, Miller SA, del Nido PJ, Beerman LB, Fuhrman BP.
Successful treatment of acute myocarditis using extracorporeal
membrane oxygenation. Crit Care Med 1993;21:302–4.
[65] Kawahito K, Murata S, Yasu T, et al. Usefulness of extracorporeal
membrane oxygenation for treatment of fulminant myocarditis and
circulatory collapse. Am J Cardiol 1998;82:910–1.
[66] Chen YS, Yu HY, Huang SC, et al. Experience and result of
extracorporeal membrane oxygenation in treating fulminant myocar-
ditis with shock: what mechanical support should be considered first?
J Heart Lung Transplant 2005;24:81–7.
[67] Grinda JM, Chevalier P, D’Attellis N, et al. Fulminant myocarditis in
adults and children: bi-ventricular assist device for recovery. Eur J
Cardiothorac Surg 2004;26:1169–73.
[68] Holman WL, Bourge RC, Kirklin JK. Circulatory support for seventy
days with resolution of acute heart failure. J Thorac Cardiovasc Surg
1991;102:932–4.
[69] Levin HR, Oz MC, Catanese KA, Rose EA, Burkhoff D. Transient
normalization of systolic and diastolic function after support with a
left ventricular assist device in a patient with dilated cardiomyopathy.
J Heart Lung Transplant 1996;15:840–2.
[70] Walters HL, Hakimi M, Rice MD, Lyons JM, Whittlesey GC, Klein
MD. Pediatric cardiac surgical ECMO: multivariate analysis of risk
factors for hospital death. Ann Thorac Surg 1995;60:329–37.
[71] Anderson HL, Attori RJ, Custer JR, Chapman RA, Bartlett RH.
Extracorporeal membrane oxygenation for pediatric cardiopulmonary
failure. J Thorac Cardiovasc Surg 1990;99:1011–21.
[72] Dalton HJ, Siewers RD, Fuhrman BP, et al. Extracorporeal
membrane oxygenation for cardiac rescue in children with severe
myocardial dysfunction. Crit Care Med 1993;21:1020–8.
[73] Kanter KR, Pennington DG, Weber TR, Zambie MA, Braun P,
Martychenko V. Extracorporeal membrane oxygenation for postop-
erative cardiac support in children. J Thorac Cardiovasc Surg
1987;93:27–35.
[74] Weinhaus L, Canter C, Noetzel M, McAlister W, Spray TL.
Extracorporeal membrane oxygenation for circulatory support
after repair of congenital heart defects. Ann Thorac Surg 1989;
48:206–12.
[75] Trittenwein G, Furst G, Golej J, et al. Preoperative ECMO in
congenital cyanotic heart disease using the AREC system. Ann
Thorac Surg 1997;63:1298–302.
[76] Goldman AP, Delius RE, Deanfield JE, de Leval MR, Sigston PE,
Macrae DJ. Nitric oxide might reduce the need for extracorporeal
support in children with critical postoperative pulmonary hyperten-
sion. Ann Thorac Surg 1996;62:750–5.
[77] Journois D, Pouard P, Mauriat P, Malhere T, Vouhe P, Safran D.
Inhaled nitric oxide as a therapy for pulmonary hypertension after
operations for congenital heart defects. J Thorac Cardiovasc Surg
1994;107:1129–35.
[78] Jaggers JJ, Forbess JM, Shah AS, et al. Extracorporeal membrane
oxygenation for infant postcardiotomy support: significance of shunt
management. Ann Thorac Surg 2000;69:1476–83.
[79] Bavaria JE, Ratcliffe MB, Gupta KB, Wenger RK, Bogen DK,
Edmunds LH. Changes in left ventricular systolic wall stress
during biventricular circulatory assistance. Ann Thorac Surg
1988;45:526–32.
[80] Ratcliffe MB, Bavaria JE, Wenger RK, Bogen DK, Edmunds LH.
Left ventricular mechanics of ejecting, postischemic hearts during
left ventricular circulatory assistance. J Thorac Cardiovasc Surg
1991;101:245–55.
[81] Secker-Walker JS, Edmonds JF, Spratt EH, Conn AW. The source of
coronary perfusion during partial bypass for extracorporeal membrane
oxygenation (ECMO). Ann Thorac Surg 1976; 21:138–43.
[82] Nowlen TT, Salley SO, Whittlesey GC, et al. Regional blood flow
distribution during extracorporeal membrane oxygenation in rabbits.
J Thorac Cardiovasc Surg 1989;98:1138–43.
[83] Kato J, Seo T, Ando H, Takagi H, Ito T. Coronary arterial perfusion
during venoarterial extracorporeal membrane oxygenation. J Thorac
Cardiovasc Surg 1996;111:630–6.
[84] Shen I, Levy FH, Benak AM, et al. Left ventricular dysfunction
during extracorporeal membrane oxygenation in a hypoxemic swine
model. Ann Thorac Surg 2001;71:868–71.
[85] Karl TR, Horton SB. Centrifugal pump ventricular assist device in
pediatric cardiac surgery. In: Duncan BW, editor. Mechanical support
J. Timothy Baldwin, B.W. Duncan / Progress in Pediatric Cardiology 21 (2006) 173–184184
for cardiac and respiratory failure in pediatric patients. New York’
Marcel Dekker; 2001. p. 21–47.
[86] Thuys CA, Mullaly RJ, Horton SB, et al. Centrifugal ventricular
assist in children under 6 kg. Eur J Cardiothorac Surg 1998;
13:130–4.
[87] Kesler KA, Pruitt AL, Turrentine MW, Heimansohn DA, Brown JW.
Temporary left-sided mechanical cardiac support during acute
myocarditis. J Heart Lung Transplant 1994;13:268–70.
[88] Chang AC, Hanley FL, Weindling SN, Wernovsky G, Wessel DL.
Left heart support with a ventricular assist device in an infant with
acute myocarditis. Crit Care Med 1992;20:712–5.
[89] Langley SM, Sheppard SB, Tsang VT, Monro JL, Lamb RK.
When is extracorporeal life support worthwhile following repair of
congenital heart disease in children? Eur J Cardiothorac Surg
1998;13:520–5.
[90] McBride LR, Naunheim KS, Fiore AC, Moroney DA, Swartz MT.
Clinical experience with 111 Thoratec ventricular assist devices. Ann
Thorac Surg 1999;67:1233–9.
[91] Korfer R, El-Banayosy A, Arusoglu L, et al. Single-center experience
with the Thoratec ventricular assist device. J Thorac Cardiovasc Surg
2000;119:596–600.
[92] El-Banayosy NR, Arusoglu L, Kleikamp G, Minami K, Korfer R.
Recovery of organ dysfunction during bridging to heart transplan-
tation in children and adolescents. Int J Artif Organs 2003;26:
395–400.
[93] Reinhartz O, Stiller B, Eilers R, Farrar DJ. Current clinical status of
pulsatile pediatric circulatory support. ASAIO J 2002;48:455–9.
[94] Shum-Tim D, Duncan BW, Hraska V, Friehs I, Shin’oka T, Jonas
RA. Evaluation of a pulsatile pediatric ventricular assist device in an
acute right heart failure model. Ann Thorac Surg 1997;64:1374–80.
[95] Hetzer R, Loebe M, Weng Y, Alexi-Meskhishvili V, Stiller B.
Pulsatile pediatric ventricular assist devices: current results for bridge
to transplantation. Semin Thorac Cardiovasc Surg Pediatr Card Surg
Annu 1999;2:157–76.
[96] Merkle F, Boettcher W, Stiller B, Hetzer R. Pulsatile mechanical
cardiac assistance in pediatric patients with the Berlin heart
ventricular assist device. J Extra Corpor Technol 2003;35:115–20.
[97] Stiller B, Lemmer J, Merkle F, et al. Consumption of blood products
during mechanical circulatory support in children: comparison
between ECMO and a pulsatile ventricular assist device. Intensive
Care Med 2004;30:1814–20.
[98] Stiller B, Weng Y, Hubler M, et al. Pneumatic pulsatile ventricular
assist devices in children under 1 year of age. Eur J Cardiothorac
Surg 2005;28:234–9.
[99] Morales DL, Dibardino DJ, McKenzie ED, et al. Lessons learned
from the first application of the DeBakey VAD Child: an intra-
corporeal ventricular assist device for children. J Heart Lung
Transplant 2005;24:331–7.
[100] Kerkhoffs W, Schumacher O, Meyns B, et al. Design, development,
and first in vivo results of an implantable ventricular assist device,
MicroVad. Artif Organs 2004;28(10):904–10.
[101] Takatani S, Hoshi H, Tijima K, et al. Tiny centrifugal blood pump
(TinyPump) for children and infants. Proc 13th Cong ISRBP
2005;55.