Heart Failure Reviews

, Volume 19, Issue 2, pp 259–266

Physiologic and hematologic concerns of rotary blood pumps: what needs to be improved?

Authors

    • Graduate School for Cellular and Biomedical SciencesUniversity of Bern
    • ARTORG Cardiovascular EngineeringUniversity of Bern
    • Thoratec Corporation
  • Siavash Asgari
    • Department of Surgery-Cardiac Section, School of MedicineYale University
  • Chris Cotter
    • Thoratec Corporation
  • Kevin Bourque
    • Thoratec Corporation
Article

DOI: 10.1007/s10741-013-9389-4

Cite this article as:
Pirbodaghi, T., Asgari, S., Cotter, C. et al. Heart Fail Rev (2014) 19: 259. doi:10.1007/s10741-013-9389-4

Abstract

Over the past few decades, advances in ventricular assist device (VAD) technology have provided a promising therapeutic strategy to treat heart failure patients. Despite the improved performance and encouraging clinical outcomes of the new generation of VADs based on rotary blood pumps (RBPs), their physiologic and hematologic effects are controversial. Currently, clinically available RBPs run at constant speed, which results in limited control over cardiac workload and introduces blood flow with reduced pulsatility into the circulation. In this review, we first provide an update on the new challenges of mechanical circulatory support using rotary pumps including blood trauma, increased non-surgical bleeding rate, limited cardiac unloading, vascular malformations, end-organ function, and aortic valve insufficiency. Since the non-physiologic flow characteristic of these devices is one of the main subjects of scientific debate in the literature, we next emphasize the latest research regarding the development of a pulsatile RBP. Finally, we offer an outlook for future research in the field.

Keywords

Ventricular assist devicesRotary blood pumpsHeart failureContinuous flowPulsatile flow

Introduction

A ventricular assist device (VAD) is a mechanical pump that helps to improve blood circulation in patients with a weakened ventricle. It typically draws blood from the apex of the left ventricle (LV) and pumps it into the circulation through the ascending aorta (Fig. 1). DeBakey [1] introduced the first successful clinical applications in the 1960s. After three decades of improvement, in the mid-1990s, they became an established treatment option for heart failure patients awaiting transplant as a bridge to transplantation (BTT) [2]. VADs can also provide long-term mechanical support as destination therapy (DT) and in a relatively small number of cases with non-ischemic etiology lead to improved cardiac function, or so-called reverse remodeling as a bridge to recovery. The first generation of VADs was based on a pneumatically or electrically driven volume displacement pump (Figs. 2a, 3). Due to the working principle analogous to the native heart with filling (diastole) and ejection (systole) phases, they provide excellent hemodynamic support. Nonetheless, their applications have substantial constraints because of their large size, invasive surgical procedure, and poor durability for long-term mechanical support [3]. These challenges necessitated the development of a new generation of VADs with simple design and improved performance.
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Fig. 1

The schematic of an implanted VAD and its components, courtesy of Thoratec Corporation

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Fig. 2

Different types of blood pumps. a HeartMate XVE (volume displacement pump), b HeartMate II (axial rotary pump), c HeartMate III (centrifugal rotary pump), courtesy of Thoratec Corporation

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Fig. 3

The schematic of a pneumatic pulsatile VAD cross-section, courtesy of Thoratec Corporation

Over the past two decades, the advent of rotary blood pumps (RBPs) as assist devices has revolutionized the field of mechanical circulatory support due to their small size (Fig. 2), silent operation, and long-term durability. Rotary pumps consist of only one moving part, the rotor, and are divided into two main categories: (1) axial flow pumps and (2) magnetically or hydro-dynamically levitated centrifugal pumps (Fig. 4). On the one hand, their operating mechanism makes it possible to achieve a reliable and durable device; on the other hand, it reduces the blood flow pulsatility owing to typical use of constant speed in clinically available devices. Despite improvements in clinical outcomes and advantages over pulsatile pumps, fundamental questions persist particularly about unknown physiologic effects of reduced arterial pulsatility in a milieu of tolerable but persisting adverse events.
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Fig. 4

a Components of an axial flow rotary blood pump, b components of a centrifugal rotary blood pump, courtesy of Thoratec Corporation

Here, we first focus on the current challenges of RBPs. Then, we review recent attempts to develop a pulsatile rotary pump, and finally, we offer an outlook for further research.

Emerged concerns

Although adverse events, including surgical mortality, right ventricular failure, neurological events, and infections, as with pulsatile devices, still persist for rotary pumps, in this section, we only focus on concerns related to working mechanism of RBPs. These include blood trauma, increased rate of non-surgical bleeding, limited cardiac unloading, vascular malformations, end-organ function, and aortic valve insufficiency.

Blood trauma

Depending on the design, miniaturized RBPs might reach rotational speeds (ω) higher than 30,000 revolutions per minute to supply enough blood flow. Upon passage through the pump, blood cells and proteins are exposed to very brief durations of high shear stress level of about 1,000 Pa (unpublished data), which are possible sources of damage to blood particles. Although the exact hematologic effects of RBPs have not been completely investigated, elevated shear forces play an important role in the incidence of thromboembolism. It is widely recognized that platelets together with a plasma protein, von Willebrand factor (vWF), play an essential role in both thrombus formation and hemostasis. Increased shear forces disturb the normal distribution of vWF molecules and may result in acquired von Willebrand syndrome. According to Sheriff et al. [4], platelets exposed to high shear stress for a short time are sensitized to subsequent lower values and activate at least 20-fold faster than particles under standard circulation conditions. Platelets and white blood cells are sensitive to mechanical stress at levels of 10 and 7.5 Pa, respectively, whereas red blood cells are less sensitive with high level of a few hundred Pa [5]. However, exposure time to mechanical force is critical for the maximum shear stress tolerable by cells. For example, 800 Pa with an exposure duration of 1 ms has been reported as the hemolytic threshold [6]; whereas another study shows that by increasing the exposure time to 700 ms, hemolysis occurs at shear stress of 255 Pa [7]. It should be noted that in normal vascular blood flow, the maximum shear stress is approximately 6 Pa occurring in the wall of arterioles [8]. These data show that devices designed based on only hemolysis tests are not optimized to reduce thrombogenicity due to high mechanical forces.

Furthermore, elevated shear stress enhances the shedding of various microparticles (MPs) from blood cells, as well as endothelial cells into circulation. These submicron particles, which are components of cells plasma membranes and bear membrane proteins of their mother cell, play an essential biologic role in inflammation, vascular injury, angiogenesis, and thrombosis [9]. A recent research study by Diehl et al. [10] demonstrates that VAD patients have elevated levels of circulating MPs, which may contribute to the occurrence of thromboembolic complications. While MPs have important physiologic and pathologic roles, their contributions to the side effects of RBPs remain unexplored. Further details about hematologic effects of RBPs are found in previous publications [11, 12].

Bleeding

Increased non-surgical bleeding, specifically in the gastrointestinal (GI) tract, is one the most frequent adverse events associated with RBPs [13]. In 2005, Letsou et al. [14] were the first to report 3 cases of GI bleeding after implantation of the Jarvik 2000 in 21 patients. By reviewing 101 VAD recipients (55 rotary and 46 pulsatile pumps), Crow et al. [15] reported almost 10-fold increases in the incidences of GI bleeding in rotary versus pulsatile devices. Additionally, based on long-term clinical studies performed between 2003 and 2011, there is sufficient evidence to demonstrate higher rates of GI bleeding event in patients supported with axial and centrifugal rotary pumps, which was not the case for patients receiving pulsatile devices [16, 17].

In an interesting study, Uriel et al. [18] tried to identify potential mechanisms for those bleeding events and investigated vWF multimers in rotary pump patients. They observed a reduction in vWF multimers of 31 patients, whereas only 18 of them (58 %) experienced bleeding. Their finding is supported by other studies that show significant loss of vWF multimers in RBP recipients, but only some patients had bleeding complications [19, 20]. A similar problem of an acquired form of von Willebrand syndrome with subsequent bleeding has been reported in patients with aortic stenosis [21]. Taken together, increased pressure inside blood vessels, high shear stress, and low pulse pressure were suggested as potential explanations for von Willebrand disease [15]. These findings indicate that loss of vWF multimers alone cannot predict bleeding risk. Although the biology and mechanism behind the bleeding is not completely understood, its higher rate associated with RBP recipients makes it rational to draw the conclusion that (1) the high-speed rotor causes damage to blood particles or (2) attenuated pulsatility plays an important role. Further research is required to identify risk factors for bleeding in these patients.

Limited cardiac unloading

A promising application of VADs besides their usage in the BTT and DT is as a bridge to myocardial recovery [22]. It was first reported by Levin et al. [23] in 1996, who found a considerable functional and structural improvement in the failing heart of a young patient after 6 months of support. It is likely that mechanical unloading stimulates the cellular biology of the myocardium and initiates recovery by alleviating the cardiac workload and relieving the biomechanical stress imposed on the cardiomyocytes [24]. Cardiac unloading is also associated with improvements in matrix metalloproteinase activity, myocyte calcium handling, and neurohormonal stimulation [25]. However, the precise mechanism by which a failing heart recovers is not completely clear.

By conducting studies on explanted human hearts, Levin et al. [26] demonstrated that ventricular dilation because of chronic cardiomyopathy could be largely reversed after 3–5 months of mechanical support. Their finding was supported by Altemose et al. [27] who observed reductions in LV chamber size and a 40 % decrease in LV mass in eight patients. The cellular basis for these changes was discussed by Zafeiridis et al. [28] who examined isolated cardiac myocytes from VAD-supported and non-supported failing hearts as well as healthy hearts. They observed that mechanical support resulted in a 28 % reduction in myocyte volume and 20 % reduction in cell length and width. In addition, myocyte contractility and its rates of shortening and relengthening improve within 3 months of circulatory support [29]. These findings indicate that cardiac workload is a major factor in pathologic cardiac hypertrophy and remodeling. Thus, mechanical unloading, which is associated with reduced wall stress, leads to favorable alterations in geometry at the organ and cellular levels of a failing heart.

A series of clinical studies demonstrates that volume displacement pumps are associated with greater LV unloading in heart failure patients compared with rotary pumps [30, 31]. This is consistent with data from animal experiments demonstrating that pulsatile pumps provide superior LV unloading and maintain a better physiologic stability [32]. This limitation of RBPs arises mainly because clinically available devices typically operate at constant speed mode confining their operating range by suction and regurgitation events. An excessive constant pump speed results in ventricular collapse, and too low speed leads to back flow of blood into the ventricle increasing cardiac workload.

Vascular malformations

Blood vessels are compliant structures that respond to physiologic conditions in terms of geometrical, structural, and functional adaptations. These adaptations are mediated in part by the vascular endothelial cells (ECs), which are directly exposed to blood flow and associated shear stress. The ECs respond to the biomechanical forces in terms of molecular signaling, gene expression, and functional changes [33]. Under normal blood flow and physiologic conditions, the fluid-induced forces are mechanotransduced into biochemical signals that result in vascular caliber regulations as well as inhibition of thrombosis and inflammation of the vessel wall. However, little is known about the impact of alterations in flow patterns and mechanical forces on ECs and vascular function in RBP patients.

In a clinical study of 20 VAD patients, Amir et al. [34] found lower endothelial function in conduit arteries and impaired peripheral vascular reactivity, most likely owing to reduced pulsatility. Westaby et al. [35] reported a decrease in medial aortic thickness and medial smooth muscle cell (SMC) number after 3 months of support with Jarvik 2000 RBP in 7 patients. SMCs play a critical role during atherogenesis, which is the developmental process of atheromatous plaques and is characterized by remodeling of arteries leading to accumulation of plaques. Other clinical studies also provide enough evidence of arteriovenous malformation highly associated with flow characteristics of RBPs [14, 16]. These clinical observations are further confirmed in animal studies where thinner aortic and arterial walls as well as a lower volume ratio of SMCs were claimed due to decreased pulsatility [36].

Furthermore, prolonged circulatory support using RBPs significantly decreases vascular pulsatility, diminishes the constrictive function of the vascular system, and increases peripheral vascular resistance, which can augment the load on the LV [36, 37]. As a result, decreased pulse pressure and changes in blood flow pattern will lead to undesirable morphological changes of aortic and arterial walls, as well as vascular surfaces, in particular, in locations such as the descending thoracic aorta and distal carotid arteries.

End-organ function

As early as the 1950s, shortly after the development of cardiopulmonary bypass, there was a substantial debate about whether the non-pulsatile perfusion provides adequate blood flow to maintain proper end-organ function [37, 38]. These early studies together with cardiopulmonary bypass experience during the last few decades suggest that short-term non-pulsatile flow is well tolerated. After the advent of rotary pumps, end-organ perfusion was a great concern; thus, many investigators examined this issue in animal models. Saito et al. [39] demonstrated that use of RBPs for a few months maintained normal end-organ function and reported no histologic abnormalities of the brain, liver, and kidney. By contrast, a number of animal experiments have shown variations in skin tissue microcirculation as well as microcirculation of the kidney and liver, including retention of blood cells, expansion of the proximal tubes, and glomerulus blood capillaries, but there is no evidence that these histologic changes impair end-organ function [40, 41]. What is more, the clinical relevance of their outcome can be ambiguous because of the use of healthy animals.

In humans, although insufficient data exist about the effects of attenuated pulsatility on end-organ function within a few years, clinical studies have shown that renal, hepatic, and neurocognitive functions are maintained within a normal range for durations up to 15 months [42, 43]. The comparison of renal and hepatic functions in patients who received a VAD as a BTT shows no major difference between continuous and pulsatile flow devices [44]. Regarding endocrine functions, there is no major effect of reduced pulsatility on the hypothalamic-pituitary end-organ system and sympathoadrenal functions [45]. Results of a study by Polska et al. [46] showed that alterations in flow pulsatility had only a small influence on blood flow in the choroid and mean flow velocities in the ophthalmic artery. In another clinical study, Kamdar et al. [47] compared the effects of centrifugal, axial, and pulsatile VADs on end-organ function for up to 3 months; their finding is consistent with recent reports by Slaughter [42] and Russell et al. [48], suggesting that RBPs supply sufficient end-organ perfusion, at least for a relatively short time support. In a recent publication, Chokshi et al. [49] provided new insight into cardiac metabolism in heart failure patients suggesting that mechanical support improves systemic and local metabolic derangements in VAD patients. This may reduce myocardial levels of toxic lipid intermediates and improve cardiac insulin signaling.

It should be noted that under most clinical conditions, RBP patients have some degree of arterial pulsatility due to native ventricular contractions. Further long-term studies preferably in randomized clinical trials are crucial to assess the effect of reduced pulsatility on pulmonary function, microcirculatory system, neuroendocrine markers, and cerebral blood flow, or metabolism.

Aortic valve insufficiency

One unexpected complication of mechanical circulatory support is the development of aortic valve lesions, which may result in commissural fusion and aortic valve insufficiency (AI). Depending on the degree of LV unloading by VAD, the aortic valve remains partially or completely closed, which increases the mechanical stress on the valve. These forces affect valvular endothelial and interstitial cells and may result in valve remodeling or pathologic alterations [50]. In addition, changes in aortic blood flow dynamics and myxoid degeneration of the aortic valve were suggested to contribute to AI development and progression [51]. AI impairs the VAD function, increases the risk of thromboembolism events, and is a great concern in potential bridge to recovery patients. Although this complication was reported during support by volume displacement pumps [52], recent studies suggest that AI is more prevalent among RBP recipients [53, 54]. Intermittently lowering the pump speed, which allow opening of the aortic valve during systole, was suggested to reduce the risk of thrombus formation in the aortic root and prevent leaflet fusion [55]. A better understanding of the RBP impact and the relationship between mechanics and valve biology will provide insights into the pathophysiology of aortic valve disease. A recent publication by John et al. [50] describes the basis for structural changes and discusses different techniques of aortic valve management during VAD support in more detail.

Towards a pulsatile rotary blood pump

As controversy remains on the long-term effects of perfusion with reduced pulsatility, speed modulation of the pump might be beneficial to restore vascular pulsatility. Besides its effect on reducing complications potentially tied to reduced arterial pulsatility, speed modulation of RBPs can effectively control cardiac workload [56, 57], which is likely important for heart recovery and device weaning. Moreover, the introduction of pulsatile RBPs would provide a unique opportunity for further research and comparison. In the literature, there are few reports describing the attempts to modulate the rotary pump’s speed, which only focus on asynchronous speed modulation [58], mathematical modeling [59], and in vitro investigation of pump speed modulation using mostly sinusoidal waveforms [60].

Bourque et al. [61] evaluated the impact of a pulsatile centrifugal pump on an ovine thoracic and abdominal aortic flow and pressure. To eliminate all native cardiac contributions to pulsatility, they replaced both ventricles with HeartMate III blood pumps. Pulsatile flow was achieved by sharply alternating the speed of the magnetically levitated rotor of the left pump between 1,500 rpm (diastole) and 5,500 rpm (systole) at a rate of 60 bpm and a systolic period of 30 %. Results showed that the mean pump-induced pulse pressure was 34 mmHg in the ascending aorta and the maximum rate of pressure rise (δp/δt) was between 189 and 238 mmHg/s, approaching that of the native pulse. Ando et al. [62] studied the effect of speed modulation of the EvaHeart RBP on myocardial perfusion in an animal model and reported an increase in coronary flow compared with the continuous mode. According to Pirbodaghi et al. [56, 57], pump speed modulation synchronized with the native heart can significantly influence myocardial energy as well as volume. Their findings indicate that high pump speed during diastole has a maximal unloading effect on LV, whereas high speed during systole increases the pulse pressure. Moreover, cardiac stroke work in the pulsatile mode could be reduced to 72 % of that in constant speed indicating the importance of the synchrony between the heart and assist device on LV unloading.

Furthermore, the controllers of some commercially available pumps (e.g. Jarvik 2000, Medos Delta stream DP3, Heartware HVAD) vary the pump speed intermittently and asynchronously to modulate the pump flow and allow better washing. Despite these initial steps toward pulsatile RBPs, more studies are required to explore the concept, determine its efficiency, and assess the importance of different prescriptive parameters.

Future considerations

While RBPs are rapidly evolving to provide destination therapy as an alternative to heart transplantation, many fundamental questions pertaining to their operating mechanisms remain to be addressed. How does the attenuated pulsatility with RBPs affect cell–cell interactions within the blood flow stream? What is its impact on blood cells margination from the center of a blood vessel toward the vascular endothelium, in particular, white blood cells that are important in the inflammatory response? How does elevated shear stress influence gene expression, extracellular and intracellular matrices? What is the impact of partial or complete unloading on myocardial blood flow and metabolism? Is there a degree of pulsatility or unloading, which may optimize myocardium recovery? In this regard, the use of combination therapies that consist of mechanical unloading and pharmacologic or biologic therapies can promote recovery in a large number of patients. It is widely known that treatment with beta-blockers and ACE inhibitors during mechanical support increases the probability of cardiac recovery. There is also preliminary evidence that stem cells from percutaneous endomyocardial biopsy specimens promote cardiac regeneration and improve heart function [63].

Among other issues, abdominal driveline infection is a major concern for long-term mechanical support, as with all VADs that have a percutaneous component [64]. Current alternatives include a transcutaneous energy transfer system (TETS) [65] to wirelessly power implantable devices and skull pedestal power delivery techniques [66]. The former has poor efficiency and suffers from technical concerns [67]; the latter requires an invasive surgery process and is associated with a low quality of life. Thus, it is necessary to develop more effective and reliable power delivery systems. Recent studies [67, 68] on wireless power transfer based on the free-range resonant electrical delivery (FREE-D) appear promising, but more research needs to be conducted in this area.

While platelet activation is critically correlated with high shear stress, its aggregation is more likely to happen at low stress levels [69], indicating that areas of stasis within the device might contribute to thrombosis formation. Thus, it is critical to identify low and high threshold stresses and completely understand the fluid dynamics of the blood inside RBPs as well as in the inflow/outflow conduits. Furthermore, platelet adhesion and thrombus formation are highly sensitive to exposed foreign surfaces. Despite advances in materials with anticoagulant function, such as heparin and hirudin, there is still no surface coating capable of completely inhibiting thrombus formation. Currently, the inlet and outlet elbows of VADs are textured to entrap particles from the blood and form a biologic coating. To eliminate the need for long-term anticoagulant therapy, which increases the incidence of side effects, the development of new antithrombogenic biomaterials is necessary for the blood-contacting surfaces of the pump and cannulas. Owing to nonthrombogenic properties of endothelial cells (ECs), coating with ECs can pave the way toward a totally nonthrombogenic surface. More investigations are needed to understand the complex molecular structures and interactions between ECs and device surfaces.

Conflict of interest

Tohid Pirbodaghi, Chris Cotter, and Kevin Bourque are R&D researchers at Thoratec Corporation in Burlington, MA, USA. The authors have no financial or personal relationships that could inappropriately influence or bias this work.

Copyright information

© Springer Science+Business Media New York 2013