Abstract
Biological applications of microfluidics technology is beginning to expand beyond the original focus of diagnostics, analytics and organ-on-chip devices. There is a growing interest in the development of microfluidic devices for therapeutic treatments, such as extra-corporeal haemodialysis and oxygenation. However, the great potential in this area comes with great challenges. Haemocompatibility of materials has long been a concern for blood-contacting medical devices, and microfluidic devices are no exception. The small channel size, high surface area to volume ratio and dynamic conditions integral to microchannels contribute to the blood-material interactions. This review will begin by describing features of microfluidic technology with a focus on blood-contacting applications. Material haemocompatibility will be discussed in the context of interactions with blood components, from the initial absorption of plasma proteins to the activation of cells and factors, and the contribution of these interactions to the coagulation cascade and thrombogenesis. Reference will be made to the testing requirements for medical devices in contact with blood, set out by International Standards in ISO 10993-4. Finally, we will review the techniques for improving microfluidic channel haemocompatibility through material surface modifications—including bioactive and biopassive coatings—and future directions.
1 Introduction
Material haemocompatibility of blood-contacting medical devices poses a major challenge to their long-term implementation (Jaffer et al., 2015). The haemocompatibilty of a material is the evaluation of the effects experienced by blood when interfaced with said material. Interactions between blood components and biomaterials contributes heavily to the process of medical device-induced thrombosis, a process which is difficult to curb once initiated (Hilal et al., 2019). The application of coatings is a crucial step in protecting the blood from material-induced damage, however their performance can vary depending on the substrate material, device dimensions and method of application (Fotovvati et al., 2019). The incorporation of new technologies—Such as microfluidics—In medical devices introduces new requirements and challenges to this process. Therefore, although previous reviews exist on the modes of action of haemocompatible coatings, there remains a lack of publications detailing microfluidic-specific applications. The growing interest in microfluidics for blood related applications can be observed by the increasing papers and patents published in this research area over the last decade, shown in Figure 1.
FIGURE 1
Number of publications (including patents) per year from 2012 until 2022 from searching Google Scholar with the term “microfluidics + blood −brain”. The results including the word “brain” were removed to exclude irrelevant organ-on-chip papers focussing on the blood-brain barrier.
1.1 Microfluidics for blood-contacting applications
Microfluidics technology is based on the different phenomena experienced by fluid manipulated in microscale channels when compared to classical fluid dynamics. Under these geometrical constraints the surface area of the channel is much greater compared to the volume of fluid flowing through the channel, resulting in a shift in the force balance and a characteristically laminar flow profile (Beebe et al., 2002). In laminar flow regimes viscous forces dominate and particles follow precise streamlines without mixing across adjacent fluid layers, and hence mass transport processes are dominated by diffusion. The resulting system has highly predictable characteristics based on convection-diffusion equations and Fick’s law, generating precise and tuneable gradients (Fan et al., 2018).
Microfluidics in the biomedical field has been dominated by diagnostics, cell and DNA analysis and organ-on-chip devices (Low et al., 2021). These platforms have the advantage of requiring less reagents, space and energy, minimising sample size. Therefore it may seem counter-intuitive for microfluidics to find use in high volume and high flow rate applications. Nonetheless, the precise control of diffusion gradients, short diffusion distances, and efficient fluidic transport in microfluidic channels have provided a window of opportunity for applications in another biomedical field: blood treatment. Research and development of microfluidic-based oxygenators and haemodialysers has grown in the past decade (Lee et al., 2008; Wei Hou et al., 2012; Potkay, 2014; Rochow et al., 2014; Kovach et al., 2015; D’Amico et al., 2017; Ausri et al., 2018; Yoon et al., 2019; Dabaghi et al., 2020; Luo et al., 2020; Gimbel et al., 2021; Lachaux et al., 2021; Santos et al., 2021).
A critical design consideration is haemocompatibility. In order to improve on current clinical devices, they must offer a less damageable experience for the blood over extended periods of time (from weeks to months). Microfluidic channels have an inherently high material surface-area to fluid volume ratio and therefore the blood-material interactions are even more pertinent. Furthermore, the small scale of microchannels means that even small thrombi can cause flow disruptions or blockage. This is therefore a key focus point to establish clinical feasibility of blood-contacting microfluidic medical devices, and a review of the literature in this field will support this research.
1.2 Common materials for microfluidic devices
Since the emergence of microfluidics for biomedical applications, the choice of device material—And related fabrication method—Has been a critical one. The most widely used materials for biomedical microfluidic devices are polymers, namely polydimethylsiloxane (PDMS) and thermoplastics, such as polystyrene (PS), polycarbonate (PC), cyclo-olefin copolymers (COC) and poly(methyl methacrylate) (PMMA). Multiple reviews have described the material properties in the context of microfluidic materials in depth (Tsao and DeVoe, 2009; Van Midwoud et al., 2012; Roy et al., 2016; Tsao, 2016; Gencturk et al., 2017; Voicu et al., 2017; Nielsen et al., 2020).
Briefly, although PDMS and thermoplastics—Particularly PS and PC, from which cell culture labware is made—Are acknowledged as biocompatible (Bélanger and Marois, 2001), this property is not evaluated in the same way as haemocompatibility (Picone et al., 2019). The definition of biocompatibility is the ability of a biomaterial to operate as intended without causing unwanted and inappropriate effects in the host (Williams, 2008). The focus of biocompatibility tests is generally in cell and tissue responses: viability, oxidative stress and enzymatic changes (Bélanger and Marois, 2001; Picone et al., 2019). A major downfall of PDMS and thermoplastics for blood-contacting applications is surface hydrophobicity (Mukhopadhyay, 2007; Tan et al., 2010; Van Midwoud et al., 2012; Gokaltun et al., 2017; Miranda et al., 2022) leading to adsorption of molecules to their surfaces and triggering coagulation pathways, as demonstrated in Figure 3. As well as absorbance concerns, PDMS is an unstable polymer with issues of unpolymerised oligomers leaching out of the material (Regehr et al., 2009; Berthier et al., 2012; Carter et al., 2020).
Gas permeability is an important consideration for blood-transporting channels to ensure blood gas levels remain between physiological limits (Beetham, 1982; Castro et al., 2022). PDMS has a high permeability to oxygen, with a coefficient of 600 Barrer (Evseev et al., 2019) or ∼2000–4000 μm2 s−1 (Berthier et al., 2012), a value much greater than the other polymers. Changes in gas distributions risks bubble formation, potentially resulting in cell membrane rupture, embolism, or disruption to flow profiles (Heo et al., 2007; Berthier et al., 2012).
In this paper we will discuss material haemocompatibility, from the initial contact between blood and biomaterial, through the mounting of the coagulation cascade and formation of thrombi. The International Standards for testing haemocompatibilty will be reviewed, in the context of microfluidics and the common materials used in the fabrication of these devices. Following from this, the practical challenges of applying haemocompatible surface treatments to microchannels and the state of the research of microchannel coatings will be discussed, with brief reference to commercially-available coatings. We will finish by predicting the future direction of haemocompatible treatments for microfluidic channels.
2 Material haemocompatibility
Blood is a characteristically heterogenous fluid, comprised of plasma and cells. Cells—Red blood cells, white blood cells, and platelets—Constitute 45% of blood volume. The main role of platelets is in haemostasis, reducing loss of blood after vessel injury. Plasma is a complex mixture of water, fats, salts and a diverse proteome (Anderson and Anderson, 2002). The active nature of the blood means that interactions with foreign materials in the bloodstream can have far-reaching and detrimental effects. It is well-documented that blood coagulation is a complex, interrelated symphony of material, mechanical, and biological factors; first conceptualised by Virchow in the mid-19th century (Virchow, 1856; Kumar et al., 2010) and revisited throughout the years (Chung and Lip, 2003; Lowe, 2003; Wolberg et al., 2012). The Virchow Triad, represented in Figure 2, combines the original elements of Virchow’s theory, adapted according to Wolberg et al. (2012). This section will focus on the interaction between the material and blood elements.
FIGURE 2
Virchow’s Triad of interacting factors which contribute to an increased risk of thrombosis. Adapted from Wolberg et al. (2012) combined with Virchow’s original translation.
2.1 Protein adsorption
Immediately upon contact with a foreign material plasma proteins are adsorbed onto the surface, the initial step in the pathway which eventually results in thrombus formation (Figure 3). The composition of the protein layer depends on the biomaterial properties and individual protein concentration—Proteins with greater affinity will displace those less attracted in a process termed the Vroman effect (Simmonds et al., 2018). Mass spectrophotometry techniques have been employed to analyse these protein films and their development over time (Xia et al., 2002; Wagner and Castner, 2004). This method identifies molecules based on their mass-to-charge ratio, through ionisation of a surface by bombardment with electrodes, then collection and characterisation of these dispersed fragments. The adsorbed proteins form a monolayer of thickness 2–10 nm (Wilson et al., 2005; Jaffer et al., 2015). On adsorption to a surface, plasma proteins undergo a conformational change, allowing them to interact with coagulation factors and blood cells—Most notably platelets (Sivaraman and Latour, 2010; Zhang et al., 2017; Horbett, 2018). The interactions have been well-documented for the most prevalent, and problematic, proteins of the adsorbed layer: fibrinogen and albumin.
FIGURE 3
Process of plasma protein adsorption to a blood-contacting biomaterial surface and ensuing platelet activation and coagulation response leading to thrombus formation.
2.1.1 Albumin
Albumin comprises about 55% of the proteome (Anderson and Anderson, 2002), and rapidly diffuses and is one of the first proteins adsorbed to surfaces, however it soon becomes displaced by the Vroman effect, being replaced by proteins with a higher affinity for the surface (Leonard and Vroman, 1992; Wilson et al., 2005). Albumin does not contain binding sites for platelets and is generally considered to be inert, which promotes its use as an option in biopassive coatings, as will be discussed later (Hylton et al., 2005). Of these higher-affinity proteins, fibrinogen has the most significant effects.
2.1.2 Fibrinogen
Fibrinogen, a major coagulation factor in plasma, plays a critical role in material contact-initiated blood activation. Under physiological conditions, soluble fibrinogen circulates in the blood in an inactive form (Hylton et al., 2005) and only on vessel injury does it reveal its coagulation properties. Following initiation, subsequent factors of the coagulation cascade are activated, leading to the generation of thrombin (Wolberg et al., 2012). Thrombin is an enzyme which catalyses the conversion of fibrinogen dissolved in plasma into fibrin fibres. These polymerise to form dense, branched networks which provide mechanical support to thrombi encompassing cells and clotting factors. In the physiological environment, these aggregates form at damage site to reduce bleeding and promote healing (Kalathottukaren and Kizhakkedathu, 2018). However, during material contact-initiated thrombosis this coagulation process contributes detrimentally. Firstly, fibrinogen is a surfactant (Horbett, 2018). It is a large molecule with many and varied side chains providing regions for bonding to biomaterial surfaces. This results in a rapid and wide-spread surface adsorption, only enhanced by conformational unfolding which increases available protein-surface interactions. This conformational change exposes platelet binding sites on fibrinogen which tethers circulating platelets to the surface—It is not the amount of adsorbed protein, but instead the shape change which mediates platelet adhesion (Sivaraman and Latour, 2010). Fibrinogen is over-represented in the adsorbed protein layer compared to its low concentration in plasma (5% of total protein content). Furthermore, fibrinogen can promote platelet adhesion even at very low concentrations on a material surface. Park et al. first identified the minimum adsorbed concentration of fibrinogen required for platelet activation on a glass-based substrate to be 20 ng/cm2, or between 2%—15% surface coverage (Park et al., 1991). The maximal platelet adhesion was reported by Tsai et al. to occur with 5–10 ng/cm2 of adsorbed fibrinogen to a polystyrene surface (Tsai et al., 1999). These values are extremely low considering that fibrinogen has been shown to adsorb from plasma to polymer surfaces between 100—200 ng/cm2 (Horbett, 2013). Adsorption of fibrinogen can be used as a measure of material haemocompatibility.
2.2 Platelet Activation
Platelets adhered to the adsorbed protein layer on biomaterial surfaces exhibit similar pro-coagulant behaviour as during platelet plug formation following vessel injury. The extrinsic coagulation pathway initiates at sites of vessel damage where tissue factor, collagen and other proteins usually contained below the vascular endothelium have become exposed to the blood (Thomas, 2019; Neubauer and Zieger, 2021). These proteins bind and activate clotting factors and circulating platelets, triggering the coagulation cascade. In normal physiology, adhered platelets must withstand the shear forces exerted by flowing blood to maintain their position at the site of vessel damage (Kamath et al., 2001). To achieve this, platelets utilise many binding points specific for extracellular matrix proteins. In the case of biomaterial contact, the adsorbed protein layer provides these docking points for platelets, leading to a similar stubborn adhesion. Once adhered, the platelets become activated, undergoing a morphological change as occurs in the formation of the platelet plug during haemostasis (Kalathottukaren and Kizhakkedathu, 2018; Thomas, 2019). Cytoskeleton remodelling dramatically alters the platelet shape to facilitate their haemostatic functions of spreading and aggregation. Through the polymerisation of actin filaments, the resting disc shape spreads with finger-like filopodial extensions, reaching up to 420% of its resting surface area (Daimon and Gotoh, 1982; Thomas, 2019). This extended morphology catches other circulating blood cells. The resulting structure rapidly covers the surface forming aggregates structurally supported by fibrin.
Another important feature of platelets is their α-granules, dense granules and lysosomes, which are rapidly released into the extracellular space on activation (Kamath et al., 2001; Blair and Flaumenhaft, 2009; Flaumenhaft and Sharda, 2018; Thomas, 2019). Granule contents include coagulants, adhesion proteins, growth factors, bioactive amines, immune mediators, chemokines, proinflammatory molecules and angiogenic factors (Flaumenhaft and Sharda, 2018). Activated platelet surface markers, such as P-selectin, initiate interactions with other cells and the material surface (Blair and Flaumenhaft, 2009). Adhesion proteins (such as fibrinogen and von Willebrand Factor) released from granules enhance these interactions. Released prothrombin contributes to the coagulation cascade in the formation of insoluble fibrin. High concentrations of pro-inflammatory chemokines are released from granules, propagating further platelet activation in a positive-feedback loop (Blair and Flaumenhaft, 2009; Thomas, 2019; Labarrere et al., 2020).
These responses of the blood on contact with biomaterials can be markers for testing of material haemocompatibility.
2.3 Evaluating material haemocompatibility with ISO 10993-4
The common polymers used for microfluidics in biomedical applications, their biocompatibility, haemocompatibility and gas permeability are summarised in Table 1.
TABLE 1
| Polymer | Biocompatibility (according to ISO 10993 or USP class VI) | Hemocompatibility | Gas permeability to O2 (Barrer) |
|---|---|---|---|
| PDMS | Biocompatible Victor et al. (2019) | Not haemocompatible Van Oeveren et al. (2002) | 600 Potkay (2014) |
| PS | Biocompatible Vesel et al. (2011) | Limited data available | 4.75 ± 0.2 Compton et al. (2010) |
| PC | Biocompatible Gómez-Gras et al. (2021) | Not haemocompatible Krishnamoorthi et al. (2023) | 1.68 Lai et al. (1993) |
| COC | Biocompatible Bernard et al. (2017) | Limited data available | 0.72–2.39 Hu et al. (2006) |
| PMMA | Biocompatible Pituru et al. (2020), Díez-Pascual (2022) | Limited data available | 0.26 Borandeh et al. (2019) |
Features of common polymers used in the fabrication of microfluidic devices for biomedical applications.
Regarding the haemocompatibility of polymers, there is lack of published data to confirm their status. In addition, even when some companies develop regulated products, they do not always disclose all the tests carried out to obtain their certification. This lack of transparency reveals the need for further research in this field, in order to produce a robust evaluation of polymer haemocompatibility. Investigations into material haemocompatibility have fallen behind those for biocompatibility, perhaps revealing a complacency in medical device research to accept biocompatibility approval as sufficient for blood-contacting applications. However, specific haemocompatibility tests are required—Listed in International Standard (ISO) 10993-4.
ISO 10993 details the biological evaluation of medical devices, with part 4 dedicated to the selection of tests for interactions with blood. The types of devices discussed in this review fall into the categories of external communicating devices directly contacting circulating blood. The standard defines a haemocompatible device or material as: “able to come into contact with blood without any appreciable clinically-significant adverse reactions”. The listed test categories check for these adverse reactions: haematology, haemolysis, platelet response, thrombosis, coagulation, and immune response. It is critical to carry out these tests under specific conditions in order to achieve relevant results.
2.3.1 Test operating conditions
According to the standard, the pre-treatment and analysis of blood samples are critical for correct interpretation of in vitro testing. Haematocrit, anticoagulant treatment, sample origins, sample preparation and storage, aeration, pH, temperature, contact surface area to sample volume ratio are listed as important variables to consider. Under dynamic test conditions, the list of variables extends to include flow rate, wall shear rate and pressure drop. The delay between blood sample collection and testing should be limited as much as possible (less than 4 h) in order to reduce non-physiological changes in blood properties.
These tests are simulated under in vitro operating conditions, replicating the blood-device interaction as closely as possible. Contact time, exposure ratio (surface area of material or device to blood volume ratio), temperature, sterility, and dynamic conditions (flow rate, shear rate, and pressure drop) should be specified to achieve this. Since the conditions in microfluidic channels are very specific, this is a crucial consideration when testing these devices.
2.3.2 Haematology
A Complete Blood Count (CBC) assesses the haematology of a blood sample. This is a standard clinical assessment carried out in medical laboratories. It returns the cell population counts, haematocrit and haemoglobin content from a blood sample via a series of tests run through a haematology analyser (Buttarello and Plebani, 2008). When compared to standard or control values this test can identify the loss of cells, either through retention on a material surface or destruction.
2.3.3 Haemolysis
Haemolysis is the rupture of the erythrocyte cell membrane. This can be biochemically-induced due to contact with the device material or changes in blood pH, temperature or nutritional factor content. Mechanical effects such as non-physiological shear stresses, turbulent flow paths or osmotic pressure differentials can induce haemolysis (Köhne, 2020). When the erythrocyte membrane ruptures haemoglobin is released into the surrounding plasma and can be detected. The level is reported as the percentage of free haemoglobin to the total haemoglobin concentration (Shin et al., 2021). Clinically, haemolysis is a concern due the loss of erythrocytes which can result in anaemia. Excessive levels of haemoglobin can induce toxic effects on organs and may also contribute to thrombotic processes. ISO 10993-4 states that it is not possible to assign a general value for pass or fail of haemolysis assessment, the situation is more nuanced. The duration of exposure to the device, consistency of haemolysis throughout its use, and comparison to alternative treatments must be considered in risk-benefit analysis.
2.3.4 Platelet status
The attachment of platelets to the surfaces of medical devices can be quantified by various techniques. Running a platelet count before and after interaction with the device quantifies total reduction in platelets. Alternatively, direct counting of adhered cells per unit area can be completed by scanning electron microscopy of the surface. This method also allows for the cell morphology to be assessed. Platelets can be labelled prior to testing and the intensity of signal (fluorescence or radiation) can be used to determine the surface-bound cells (Weber et al., 2018; Braune et al., 2019). A similar method indirectly quantifies the platelet adhesion through apoptosis assays, such as LDH (lactate dehydrogenase). However, it must be noted that for these indirect tests platelet-rich plasma should be used rather than whole blood, otherwise the cell type is not certain.
Flow cytometry analysis is the most common method for determining the active state of a platelet population through detection of the membrane markers P-selectin (CD62) or CD42b which are expressed only when activated (Braune et al., 2019). Assays can be carried out to quantify soluble granule contents released by activated platelets, such as the amount of Platelet Factor 4 (PF4) or β-thromboglobulin (Braune et al., 2019). Alternative methods include qualitative investigation of platelet morphology with scanning electron microscopy.
2.3.5 Coagulation
The coagulation status of blood after contact with materials can be investigated through the generation of thrombin and fibrin, the major proteins of the pathway. This can be achieved by conducting ELISA for thrombin-antithrombin complex and fibrinopeptide A respectively (Braune et al., 2019).
2.3.6 Immune response
According to ISO 10993-4 the immune response takes into account the complement system and leukocyte functions (Weber et al., 2018; Braune et al., 2019). The number of leukocytes in a blood sample is reported in the CBC, and their adhesion to the material surface can be quantified by the same approach as for platelets. The active state of leukocytes is confirmed through the detection of PMN elastase, an enzyme secreted by activated leukocytes as part of the inflammatory response (Lee and Downey, 2001). The complement system activity is determined by the presence of proteins which are activated in a cascade during an immune response (Dunkelberger and Song, 2010). Since there are different pathways by which the complement system can be triggered, either protein C3a—Which is common to all pathways—Or the terminal product SC5b-9 is investigated. Their detection can determine if the complement system is active and the immune response has been mounted.
2.3.7 Limitations of haemocompatibility tests
Due to the micron scale dimensions, microfluidic channels are less tolerant to blockages and even minimal surface deposition can dramatically affect the hydrodynamic forces and therefore the device operation. There is a need to develop microfluidic-specific tests, or adapt the current ISO test recommendations to the operation of these devices, in order to ensure appropriately haemocompatible devices. The testing method outlined in this standard is only sufficient in investigating blood-biomaterial interaction and are limited in their ability to predict a device’s holistic effect on the blood.
When considering erythrocytes, haemolysis is the standard ISO test to confirm material haemocompatibility, however it represents a high level of destruction to red blood cells which occurs in extreme conditions (Gusenbauer et al., 2018). The measurement does not consider the damages imposed prior to membrane rupture: pore formation, tether formation, changes to cell shape and membrane flexibility (Grigioni et al., 2005). This sublethal damage can result in early removal of cells from the bloodstream and consequently low haematocrit can result in anaemia (Olia et al., 2016). Although not included in ISO 10993-4, these effects can be identified by investigating red blood cell deformability through micropipette aspiration, viscometry or optical methods (Olia et al., 2016). The inclusion of sublethal damage tests would improve on current haemolysis detection techniques.
In extracorporeal devices, the entire blood volume will pass through before re-entering the vasculature and continuing circulation in the body. Therefore the damage to the blood will not be equivalent to the same volume of blood being repeatedly circulated through the device. However, it must also be noted that these devices are intended for long term use and therefore any deposition of blood products on the channel surfaces will contribute to a build-up over time.
The flow element part of Virchow’s triad provides another avenue for design optimisation and testing through computational modelling. This is particularly interesting in microfluidic devices where the flow conditions are highly specific, predictable, and can be manipulated with close precision. The methods by which this can be achieved have been summarised in a recent review (Feaugas et al., 2023).
3 Blood-protective coatings
Coating of biomedical materials is standard practice for devices in contact with blood: from basic tubing to heart valves, stents and ECMO circuits. However, this remains a hurdle for new devices seeking clinical approval and development of haemocompatible coatings is an area of active research (Hedayati et al., 2019). This section will cover the unique challenges when coating microfluidic channels, pre-treatment of surfaces with plasma exposure, the haemocompatible coatings which have been applied to microchannels, and finally commercially-available coatings.
3.1 Challenges in coating microchannels
Typical well-established surface coating methods include dip-coating, spray-coating and physical/chemical vapour deposition (Fotovvati et al., 2019). Microfluidic channels pose unique challenges which may deem these methods inappropriate, or else require substantial adaptions. Considering that most microfluidic chips are fabricated by the ‘sandwich’ method of creating open channels and then bonding them to a base substrate to seal (Convery and Gadegaard, 2019), coatings can be applied before or after this bonding step—With each approach bringing its own benefits and challenges, summarised in Figure 4.
FIGURE 4
Differing coating applications to open (left side) and sealed (right side) microchannels, with practical features of each: benefits and challenges.
Coating of open channels (prior to bonding) provides direct access to the target surface which is more likely to support the use of traditional techniques and equipment, and broadens the viable methods. Furthermore, verification of coating coverage can be carried out more reliably on an exposed surface where fluorescent and microscopy techniques can be employed. However, many traditional coating methods cover the material surface totally and non-specifically, but in microfluidics it is only the inner channel surface that requires coverage. Coatings applied to the substrate area around the channels is likely to alter bonding properties due to changed surface chemistry. Since sealing is already a major challenge further complications should be avoided (Tsao, 2016). In parallel, bonding often requires surface pre-treatment (Tsao and DeVoe, 2009; Sivakumar and Lee, 2020) which may interfere with the coating. To apply the coating only to the inner channel area requires microscale precision to deposit only on target areas.
To overcome this, microchannels may be coated after sealing. This approach, however, would require a fluidic coating method which can enter the channels via the inlets and outlets. As these devices have controlled operational conditions (such as hydraulic pressure and resistance) and the coatings often have their own requirements (such as exposure time and mode of reaction) and fluidic qualities (such as viscosity and chemical composition) it can be difficult to achieve a reliable coverage. Many surface treatment methods require direct interaction with the surface and are incompatible with a closed channel approach, such as plasma treatment (Sundriyal et al., 2020). Additionally, evaluation of coverage is difficult to achieve without opening the channels.
3.2 Plasma treatment
An initial step in polymer surface treatment is to increase the hydrophilicity. Plasma treatment (with either oxygen or air) can achieve this by degrading contaminants on the surface and introducing oxygen-containing functional groups (Lai et al., 2006). Plasma treatment directs high energy ions towards the surface, breaking organic bonds which are free to react with oxygen species in the gas to result in a negatively-charged surface with increased hydrophilicity (Yu et al., 2015; Iqbal et al., 2019; Primc, 2020; Jiang et al., 2022). However this method alone does not provide sufficient haemocompatibility (Recek et al., 2014), mainly due to hydrophobic recovery of the material or incomplete coverage of oxygen-containing groups (Mukhopadhyay, 2007; Zhou et al., 2012; Zahid et al., 2017). Therefore it is often used in combination with other haemocompatible coatings. The free radicals on the material surface after plasma treatment can be reacted with other molecules to cover the surface (Sharma et al., 2007; Shakeri et al., 2019; Özgüzar et al., 2022). Since plasma treatment is already a crucial step in microfluidic device fabrication, it positions this as a convenient and accessible option for surface pre-treatment. A plasma machine is a fundamental piece of equipment in microfabrication laboratories and its effects can be utilised simultaneously for bonding, cleaning and surface treatment purposes (Zhou et al., 2012; Sundriyal et al., 2020; Hassanpour-Tamrin et al., 2021).
3.2.1 Polymer stability
As previously mentioned, PDMS stability is a major concern when used in biomedical applications. Low molecular weight chains migrate from the interior of the PDMS to the surface by diffusion (Bodas and Khan-Malek, 2007), resulting in a return of the material’s original hydrophobic properties (Lillehoj and Ho, 2010; Long et al., 2017; Trantidou et al., 2017). This can occur rapidly, from hours to days after surface modification, questioning its suitability for longer term biomedical use. It has been reported that after surface hydrophilisation by plasma treatment, the hydrophobic surface returns after 30 min to 2 h—Depending on the plasma parameters used (Stauffer, 2014; Long et al., 2017). As already discussed, PEGylation of the PDMS surface improves its hydrophilic stability (Lai and Chung, 2020), but the polymer can be further stabilised through modification of its structure with PEG. The addition of PEG to uncured PDMS results in a stable surface hydrophilicity for up to 20 months (Gökaltun et al., 2019).
COC polymers also have stability issues. After plasma oxygenation, they are only stable for a few hours before returning to their hydrophobic character due to the reorganization of the polymer or contamination by air (Lee et al., 2015).
PC, a polymer, that is, neither strongly hydrophilic nor hydrophobic, is also one of those polymers whose hydrophilic nature can be improved by treatments, but not permanently. On the other hand, it is possible to stabilize it for at least 1 year by modifying its surface by reaction with branched polyethyleneimine as well as with a poly(ethylene-alt-maleic anhydride) anhydride and then by the hydrolysis of the anhydride groups (Jankowski and Garstecki, 2016). The PC surface thus contains a large amount of carboxyl groups.
Increasing the power intensity of the oxygen plasma treatment improves the stability time of PC and PS. Following treatment with a self-polarization voltage between 480 and 600 V, the polymers are still hydrophilic even after 6 months of storage (Larsson and Dérand, 2002).
The stability of PMMA surface hydrophilicity is improved this time by plasma treatment followed by fixation of polyvinylalcohol (PVA). In dry storage conditions, the PMMA could keep a contact angle between 10° and 20° for at least 1 month post-treatment. Tests were only conducted after 30 days so the stability beyond this period is still to be investigated (Yu et al., 2015).
3.3 Types of coating
3.3.1 Heparin
Bioactive haemocompatible coatings harness the pharmacological properties of anticoagulant molecules to intervene with thrombotic pathways. Heparin is a very common and widely used anti-coagulant drug in clinical medicine and is the gold-standard coating of medical devices, from general tubing to vascular stents and extracorporeal devices (Olsson and Larm, 1991; Biran and Pond, 2017; Jaffer and Weitz, 2019). It is a molecule based on heparan sulphate expressed on the surface of endothelial cells where it binds with anti-thrombin to counteract thrombin’s platelet stimulation (Kuchinka et al., 2021). The catalytic mode of action of heparin is the same, it binds anti-thrombin at a specific active site (Casu, 1985). It is therefore crucial that this active penta-saccharide sequence found at the end of the heparin molecule is freely available for bonding with anti-thrombin. This adds further challenge to the method by which heparin can be attached to a substrate. Heparin has been immobilised on polymer surfaces by different methods, requiring initial activation or surface functionalisation which includes polymer brush spacers, protein layers or amination (Magoshi and Matsuda, 2002; Michanetzis et al., 2003; Olander et al., 2003; Chen et al., 2005; Linhardt et al., 2008; Du et al., 2011; Kolar et al., 2015; Biran and Pond, 2017; Özgüzar et al., 2022). These will be covered in the following sections.
Heparin treatment, however, does have drawbacks. The most severe is heparin-induced thrombocytopenia (HIT), a condition whereby the patient’s immune cells are triggered to activate platelets on contact with heparin (Hilal et al., 2019). This has a rapid, pro-coagulant effect on the blood, forming clots which can have severe effects. HIT occurs in approximately 2.5% of patients, with a greater risk during recurring heparin treatments (Maul et al., 2016)—Such as during extra-corporeal therapies. It must also be noted that heparin operates by thinning the blood, therefore there is the associated risk of uncontrolled bleeding.
3.3.2 Albumin
Biopassive coatings aim to eliminate protein adsorption to the surface from first contact with blood, stopping initiation of coagulation cascade. They act through “stealth” techniques—Rendering the material surface inert. One such method is blocking by albumin (Sweryda-Krawiec et al., 2004; Hylton et al., 2005; Yamazoe et al., 2010; Zhang et al., 2013; Krajewski et al., 2015; Park et al., 2017). Albumin is the most abundant plasma protein and its structure does not possess platelet-binding sites. Intentional saturation of the material surface with albumin creates a protective layer which blocks binding of other proteins and the ensuing activation of coagulation pathways (Hylton et al., 2005). It can be applied as a solution through sealed channels making it well-suited for coating of microfluidic networks (Schrott et al., 2009; Convert et al., 2012; Azizipour et al., 2022). Furthermore, surface pre-treatment is not required for this method of coating (Guha Thakurta and Subramanian, 2011; Park et al., 2017). However, albumin can denature, dissolve or be displaced by fibrinogen over time, triggering the pathways described earlier (Amiji et al., 1992; Zelzer et al., 2012; Buddhadasa et al., 2018; Hasan et al., 2018). Albumin alone is considered better suited to short term applications, but can be used in combination with other strategies to improve its durability.
3.3.3 Polymer brushes
Polymer layers can be added to surfaces to limit protein adsorption, often referred to as polymer brushes because of their adhesion to the surface at one end of the chain (Buhl et al., 2020). Polymers based on the ethylene glycol unit, such as polyethylene glycol (PEG) and Poly (ethylene oxide) (PEO) (Leckband et al., 1999), are commonly bonded to surfaces as coatings to prevent non-specific protein fouling (Israelachvili, 1997; Wei et al., 2014; Fischer et al., 2018). This process is often referred to as PEGylation and has been achieved on the channels of PDMS microfluidic devices by plasma pre-treatment (Sharma et al., 2007) or integration as a copolymer additive (Gökaltun et al., 2019). PEGylated PDMS microchannels exhibit improved haemocompatibility—With reduced fibrinogen adsorption, platelet adhesion and platelet activation when compared to bare surfaces (Yeh et al., 2012; Kovach et al., 2014; Plegue et al., 2018; Gökaltun et al., 2019). This is accredited to the hydrophilic properties of PEG-based materials, whereby hydrogen bonds to the surface, creating a steric repulsion and a physical water barrier to reduce surface fouling (Chen et al., 2010; Long et al., 2017; Thon et al., 2017; Plegue et al., 2018).
Polymer brushes have also found application as spacers through immobilisation of specific molecules to the free end of the polymer chain, exposing it to the contacting blood (Wong and Ho, 2009; Wei et al., 2014; Kolar et al., 2015). PEG has reactive terminal hydroxyl groups which provide a platform for grafting of bioactive molecules or with other polymers to improve the coating properties. When used in this way, polymer brushes provide a secure grafting to the material surface and an end-point which can interact with the desired molecule. The bio-inspired polydopamine (PDAM) has gained interest for having great potential as a method of surface functionalisation by this approach (Liu et al., 2014; Madhurakkat Perikamana et al., 2015; Ding et al., 2016; Kanitthamniyom and Zhang, 2018; Ryu et al., 2018; Lee et al., 2019).
Originally inspired by the ability of mussels to securely adhere to multiple surfaces in harsh environmental conditions, PDAM-based coatings have been applied to polymers to improve their haemocompatibility (Yang et al., 2012; Ye et al., 2015; Li et al., 2020; Tan et al., 2021). Microfluidic channel surfaces have been functionalised with PDAM through self-polymerising methods in closed channels (Shen et al., 2015; Kanitthamniyom and Zhang, 2018; Khetani et al., 2020; Park et al., 2022). The current overriding application of PDAM is as a spacer to create a very secure and simple anchor point for other molecules (Luo et al., 2013), including bioactive anticoagulants, such as heparin (Leung et al., 2015).
3.3.4 Zwitterionic polymers
Zwitterionic polymers have both positive and negative charges, from cation and anion-containing groups respectively, while the overall charge is neutral (Sin et al., 2014; Blackman et al., 2019). The incentive to apply these polymers as a biocompatible surface layer comes from the similar dual-charge of the phospholipid membrane of mammalian cells (Schlenoff, 2014). Zwitterionic groups—Most commonly sulfobetaine, carboxybetaine, phosphobetaine and phosphorylcholine—Can be integrated to polymers referred to as polybetaines or polyzwitterionic materials (Chen et al., 2010; Schlenoff, 2014; Sin et al., 2014; Blackman et al., 2019). These polymers can be grafted to material surfaces and exert anti-fouling properties, increasing the surface hydrophilicity and forming a hydrated boundary layer—The same phenomenon which occurs at PEGylated surfaces (Chen et al., 2010; Schlenoff, 2014). Grafting of zwitterionic polymers on PDMS surfaces has exhibited improved haemocompatible properties: reducing fibrinogen adsorption, platelet deposition and haemolysis (Leigh et al., 2019; Kim et al., 2020; Jensen et al., 2021; McVerry et al., 2022; Mercader et al., 2022). Furthermore, grafting has been achieved on the inner surfaces of microfluidic channels (Plegue et al., 2018; Mercader et al., 2022) which suggests their applicability as a coating in microfluidic blood-contacting devices.
3.4 Commercial coatings
There are various blood-protective coatings commercially available, developed by medical device companies for use in coating of their medical devices such as cardiopulmonary bypass circuits (CPB). These commercial coatings, their mechanism of action (as biopassive, bioactive or combination), the molecular components, and the current applications are summarised in Table 2.
TABLE 2
| Company | Commercial name | Mechanism of action | Coating component | Current applications | References |
|---|---|---|---|---|---|
| Medtronic | Balance™ Biosurface | Combination | Polyethylene oxide (PEO); sulphate and sulphonate groups | CPB circuits | Teligui et al. (2014),Willers et al. (2021) |
| Trillium® Biosurface | Combination | Heparin; PEO; sulphate and sulphonate groups | CPB circuits | Biran and Pond (2017),Hong and Waterhouse (2023) | |
| Terumo | Xcoating™ | Biopassive | Poly(2-methoxyethylacrylate) (PMEA) | CPB circuits, haemodialysers, catheters | Biran and Pond (2017) |
| Maquet Getinge group | BIOLINE | Bioactive | Heparin; albumin | CPB circuits, vascular graft | Hoshia et al. (2013),Biran and Pond (2017) |
| SAFELINE | Biopassive | Albumin | CPB circuits | Preston et al. (2010),Zhang et al. (2021) | |
| SOFTLINE | Biopassive | Glycerol-poly(ethylene glycol)-ricinoleate | CPB circuits | Zhang et al. (2021) | |
| LivaNova | PHISIO | Biopassive | Phosphorylcholine | CPB circuits, oxygenators | De Somer et al. (2000),Hei et al. (2023) |
Commercial blood-protective coatings, their mechanism of action and the molecular components employed to achieve this, and the devices on which they are currently applied.
The coatings from Medtronic (Balance™ Biosurface & Trillium® Biosurface) differ only in the presence of heparin. They both consist of a primer layer on which is fixed polyethylene oxide (PEO) chains which deems the surface hydrophilic. The addition of sulphonate and sulphate groups contributes a negative-charge to repel platelets and also binds antithrombin to reduce thrombin production. Heparin, present only on the Trillium® Biosurface coating, increases the anti-coagulant activity (Medtronic, 2020).
The Maquet Getinge group uses three coatings: SAFELINE, SOFTLINE, and BIOLINE. The SAFELINE and SOFTLINE coatings do not contain heparin and their mechanism of operation is passivation. For SOFTLINE, this is particularly unique, utilising the hydrophilic polymer glycerol-poly(ethylene glycol)-ricinoleate with hydrophilic polymers. SAFELINE and BIOLINE are albumin-based, with BIOLINE being the bioactive option combining the addition of heparin (Getinge, 2018).
Xcoating™ and PHISIO, from the companies Terumo and LivaNova respectively, are both heparin-free coatings, of which only the hydrophilic nature prevents blood coagulation. However, they achieve this with two different polymers: PMEA poly(2-methoxyethylacrylate) for Xcoating™ and phosphorylcholine for PHISIO. Both of which reduce protein denaturation and platelet adhesion (Terumo, 2018; LivaNova, 2023).
3.5 Future prospects for haemocompatible coatings of microchannels
3.5.1 Endothelialisation
The future direction of haemocompatible coatings in microfluidic channels is following a biomimetic approach. One highly anticipated method is lining channels with endothelial cells. Within the body, the inner surface of the vascular network is lined with endothelial cells to form an inherently haemocompatible monolayer (Neubauer and Zieger, 2021). Vascular endothelial cells regulate blood haemostasis through multiple anticoagulant, antithrombotic and procoagulant mechanisms. The biologically-relevant dimensions of microfluidic channels places them as a potential candidate for endothelialisation (Hesh et al., 2019).
The aspiration is such that the blood will not recognise a change in environment from exiting the vessels of the body to the lined channels of the device (Hesh et al., 2019). The use of patient-derived cells to create a personalised device would reduce the risk of adverse reactions and further improve haemocompatibility. However major challenges face this approach. Since endothelial cells are very reactive to shear stress and hydrodynamic conditions the operational flow conditions must be closely controlled to avoid cellular detachment or disturbing the integrity of the monolayer (Roux et al., 2020). Furthermore, the attachment surface must be prepared for long-term cell culture (Jana, 2019). Depending on the substrate material it will require some kind of base coating to encourage cell adhesion and to support the culture. Maintenance of the culture is also an important consideration. Controlled removal and renewal of dead cells is required to ensure an operational and complete coating. The regulatory pathway to bring a cell-based coating to market will be challenging. Some characteristics of endothelium anti-coagulant activity has inspired research into new approaches for haemocompatible coatings. Although some microfluidic networks have been endothelialised (Burgess et al., 2009; Hellmann et al., 2020; Lachaux et al., 2021) significant progress is required before it is a feasible clinical option.
3.5.2 NO-releasing
Nitric Oxide (NO) is a soluble gas continuously produced and released into the blood by endothelial cells to regulate platelet activity, reducing their adhesion and aggregation to play a crucial anti-thrombotic role (Radomski et al., 1987; Emerson et al., 1999; Tousoulis et al., 2011; Porrini et al., 2020; Neubauer and Zieger, 2021). NO also modulates the inflammatory response (Kobayashi, 2010), T-cell mediated immunity (Bogdan, 2015; García-Ortiz and Serrador, 2018) and exhibits antibiotic properties (Wang et al., 2002). This response has been replicated in NO-releasing materials (Wu Y. et al., 2007b; Wu et al., 2007a; Seabra et al., 2010; Yang et al., 2015; Liu et al., 2017; Simon-Walker et al., 2017; Luo et al., 2018; Qiu et al., 2019; Sadrearhami et al., 2019; Devine et al., 2020; Lyu et al., 2020; Hosseinnejad et al., 2021; Mondal et al., 2021). Although their application to microchannels is limited so far, such coatings have been investigated for other biomedical applications, the use of polymers as base substrate means they are still relevant in the development of microfluidic devices. These approaches generally operate through the inclusion of a NO donor integrated into the coating matrix or immobilised on the material surface, the most common being S-Nitroso-N-acetylpenicillamine (SNAP) (Liu et al., 2017; Devine et al., 2020; Mondal et al., 2021), S-nitrosothiols (RSNOs) (Yang et al., 2015; Luo et al., 2018; Qiu et al., 2019; Hosseinnejad et al., 2021) or N-diazeniumdiolate precursors of NO (Wu B. et al., 2007a; Sadrearhami et al., 2019). Immobilisation can be achieved by grafting to protein spacers, as previously discussed (Liu et al., 2017). In attempts to further replicate the antithrombotic properties of the endothelium, these methods are often integrated with immobilised heparin (Wu B. et al., 2007a; Simon-Walker et al., 2017; Devine et al., 2020), which takes the place of endothelial heparan sulphate. However, the ability to control the release of NO over time is limited by the fact the molecule is highly reactive with a very short half-life. In the blood this is within the range of seconds (Weller, 2009; Fleming et al., 2017). This is also the case with the release of NO from N-diazeniumdiolate, where the half-life is only a few minutes, introducing technical difficulties with its manipulation (Jeong et al., 2018).
In an attempt to overcome this unstable release there is the alternative approach of introducing NO, instead in gaseous form. This is particularly relevant for microfluidics due to the efficient gas exchange capabilities in these devices (Thompson et al., 2020). The inclusion of NO in the sweep gas blend in oxygenators has previously gained interest in clinical settings, particularly in patients with severe respiratory conditions where there is some evidence that it improves oxygenation capabilities and reduces platelet activation (Mellgren et al., 1996; Keh et al., 1999; Skogby et al., 2003). However, more recent studies have called these results into question, revealing negligible effects or minimal improvements to blood condition after the addition of NO to the sweep gas during ECMO (Adhikari et al., 2007; Rossidis et al., 2020; Niebler et al., 2021; Fallon et al., 2022). Furthermore these therapies require further definition regarding the release flux of NO into the blood [the in vivo range for vascular endothelium is 0.5–4 × 10−10 mol cm−2 min −1 (Vaughn et al., 1998)], since excessive levels can lead to detrimental effects including heart failure, blood pressure changes and neural defects (Khazan and Hdayati, 2014).
4 Discussion
Coatings are a critical part of improving haemocompatibility of blood-contacting devices. Since the emergence of polymeric microfluidic devices as new platforms for manipulating blood under predictable hydraulic conditions, the application of coatings to these devices must be considered. Until now the focus has been primarily on the mechanical experience of the blood and blood-processing functionalities, with the material interactions remaining an afterthought. Although it is true that haemodynamic forces contribute hugely to damage experienced by blood in microfluidic networks, and the methods of protective design have been previously reviewed (Szydzik et al., 2020; Astor and Borenstein, 2022; Feaugas et al., 2023), devices will not achieve acceptable haemocompatibility without appropriate coating of microchannel surfaces. This review provides a foundational understanding of the significance of material-blood interactions in microfluidic channels and the formation of thrombi, and how coatings can improve haemocompatibility.
Since their conception, materials and fabrication of microfluidic devices have represented a major bottleneck to their commercialisation (Roy et al., 2011; Temiz et al., 2015; Nielsen et al., 2020). In the context of blood-contacting microfluidics this is even more pertinent since the most common materials—Polymers hailed for their improved fabrication qualities—Promote thrombogenic pathways. However, as noted in the lack of publications and data in Table 1, haemocompatibility is not a priority during testing with the focus being biocompatibility instead. The two characteristics are not interchangeable, they have very different parameters and requirements. It is clear that there is more research needed to verify the haemocompatibility of these polymers—Not only for microfluidics but for blood-contacting medical devices in general.
The multi-step fabrication processes of microfluidic devices require pre-treatment or surface modification steps which challenge the application or introduction of coatings. This represents a major limitation to the methods by which coatings can be applied to the microchannels, and must be considered before selecting the coating. From a fabrication perspective, it is more simple to apply the coating after sealing the microchannels in order to preserve bonding integrity. However, for this to work the coating must be fluidic and applicable through the inlet and outlet ports.
In general, haemocompatible coatings take inspiration from the endothelium. Heparin remains the gold standard for clinical blood protective coatings, positioning it as the first port-of-call for coating microfluidic channels too. However, trends in research are moving away from this coating method and towards “heparin-free” options which, as discussed, are showing promising results.
Microfluidic devices offer new platforms where diffusion gradients can be closely controlled. This has incentivised their application to blood processing medical devices, such as oxygenators or dialysers. The most common microfluidic materials are polymers, such as PDMS, which are poorly suited to this application since their surfaces promote thrombogenic processes. Furthermore, the geometry of microchannels is such that the surface area to volume ratio is shifted: there is a high contact between the flowing fluid and material walls. It is therefore critical that the surface be altered to protect the blood and improve device haemocompatibilty.
Coatings applied to blood-contacting medical devices have been shown to greatly reduce blood trauma during their use and is standard clinical practice. However, the process of coating microfluidic channels is not without challenges. The coating application method is limited by the fabrication and assembly process, or vice versa. In addition, the shear forces exerted by fluids on microchannel surfaces can challenge the integrity of the coating and it must be ensured to withstand the dynamic environment. Plasma cleaning is a crucial step in the fabrication of microfluidic devices, mostly in order to activate the surface for bonding but critically to remove debris or impurities. Activation of the material surface by plasma is often also the first step in the coating process by freeing functional groups for bonding with the coating molecules.
Heparin is considered the gold standard in anti-coagulant coatings, it is a bioactive molecule which is often immobilised on surfaces via polymers or protein anchors. One such protein is albumin. This readily available protein can be adsorbed rapidly to hydrophobic polymer surfaces to block unwanted adsorption of plasma proteins, however it is displaced over time. A major method of biopassive coatings is the grafting of polymers. The most common being PEG-based, hydrophilic polymers which create a hydrated layer at the surface which reduces blood-material interactions. Polymer brushes, including PDAM, can also function as spacers to attach molecules—Such as heparin—To material surfaces to render them haemocompatible. Zwitterionic polymer coatings mimic the dual-charge phenomenon of the cell membrane to repel protein and cells from surfaces.
The ideal coating would of course be the endothelial layer itself. Some progress has been made to coat networks of microchannels with cells but further research is required to support this approach in clinical devices of the future. Recently, haemocompatible coatings have employed other biomimetic approaches which replicate the activity of the endothelium, one focus being NO-releasing coatings. It is clear that future haemocompatible coating developments will integrate protective features of the natural endothelium in order to provide a truly biomimetic, inert surface for interaction with blood.
The evolution of microfluidics technology towards high volume blood processing involves new considerations and challenges to achieve surface haemocompatibility.
Statements
Author contributions
GN conceived and wrote the manuscript. AL contributed in writing the manuscript. WA, TF, SC, and ER contributed in reviewing the manuscript. CP, WA, CMP, and MB reviewed and structured the manuscript, and managed the project. All authors contributed to the article and approved the submitted version.
Conflict of interest
Authors GN, WA, SC, TF, ER, CMP, and CP were employed by the company Eden Tech.
The remaining authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.
Publisher’s note
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References
1
AdhikariN. K. J.BurnsK. E. A.FriedrichJ. O.GrantonJ. T.CookD. J.MeadeM. O. (2007). Effect of nitric oxide on oxygenation and mortality in acute lung injury: systematic review and meta-analysis. Br. Med. J.334, 779–782. 10.1136/bmj.39139.716794.55
2
AmijiM.ParkH.ParkK. (1992). Study on the prevention of surface-induced platelet activation by albumin coating. J. Biomater. Sci. Polym. Ed.3, 375–388. 10.1163/156856292x00196
3
AndersonN. L.AndersonN. G. (2002). The human plasma proteome: history, character, and diagnostic prospects. Mol. Cell. Proteomics1, 845–867. 10.1074/mcp.R200007-MCP200
4
AstorT. L.BorensteinJ. T. (2022). The microfluidic artificial lung: mimicking nature’s blood path design to solve the biocompatibility paradox. Artif. Organs46, 1227–1239. 10.1111/aor.14266
5
AusriI. R.FeyginE. M.ChengC. Q.WangY.LinZ. Y. W.TangX. S. (2018). A highly efficient and antifouling microfluidic platform for portable hemodialysis devices. MRS Commun.8, 474–479. 10.1557/mrc.2018.43
6
AzizipourN.AvazpourR.SawanM.RosenzweigD. H.AjjiA. (2022). Uniformity of spheroids-on-a-chip by surface treatment of PDMS microfluidic platforms. Sensors Diagnostics1, 750–764. 10.1039/d2sd00004k
7
BeebeD. J.MensingG. A.WalkerG. M. (2002). Physics and applications of microfluidics in biology. Annu. Rev. Biomed. Eng.4, 261–286. 10.1146/annurev.bioeng.4.112601.125916
8
BeethamR. (1982). A review of blood pH and blood-gas analysis. Ann. Clin. Biochem.19, 198–213. 10.1177/000456328201900402
9
BélangerM. C.MaroisY. (2001). Hemocompatibility, biocompatibility, inflammatory and in vivo studies of primary reference materials low-density polyethylene and polydimethylsiloxane: a review. J. Biomed. Mat. Res.58, 467–477. 10.1002/jbm.1043
10
BernardM.JubeliE.BakarJ.TortolanoL.SaunierJ.YagoubiN. (2017). Biocompatibility assessment of cyclic olefin copolymers: impact of two additives on cytotoxicity, oxidative stress, inflammatory reactions, and hemocompatibility. J. Biomed. Mat. Res. - Part A105, 3333–3349. 10.1002/jbm.a.36199
11
BerthierE.YoungE. W. K.BeebeD. (2012). Engineers are from PDMS-land, biologists are from polystyrenia. Lab. Chip12, 1224–1237. 10.1039/c2lc20982a
12
BiranR.PondD. (2017). Heparin coatings for improving blood compatibility of medical devices. Adv. Drug Deliv. Rev.112, 12–23. 10.1016/j.addr.2016.12.002
13
BlackmanL. D.GunatillakeP. A.CassP.LocockK. E. S. (2019). An introduction to zwitterionic polymer behavior and applications in solution and at surfaces. Chem. Soc. Rev.48, 757–770. 10.1039/c8cs00508g
14
BlairP.FlaumenhaftR. (2009). Platelet α-granules: basic biology and clinical correlates. Blood Rev.23, 177–189. 10.1016/j.blre.2009.04.001
15
BodasD.Khan-MalekC. (2007). Hydrophilization and hydrophobic recovery of PDMS by oxygen plasma and chemical treatment-An SEM investigation. Sensors Actuators, B Chem.123, 368–373. 10.1016/j.snb.2006.08.037
16
BogdanC. (2015). Nitric oxide synthase in innate and adaptive immunity: an update. Trends Immunol.36, 161–178. 10.1016/j.it.2015.01.003
17
BorandehS.AbdolmalekiA.Zamani NekuabadiS.SadeghiM. (2019). Methoxy poly(ethylene glycol) methacrylate-TiO2/poly(methyl methacrylate) nanocomposite: an efficient membrane for gas separation. Polym. Technol. Mat.58, 789–802. 10.1080/03602559.2018.1520255
18
BrauneS.LatourR. A.ReinthalerM.LandmesserU.LendleinA.JungF. (2019). In vitro thrombogenicity testing of biomaterials. Adv. Healthc. Mater8, 1900527. 10.1002/adhm.201900527
19
BuddhadasaM.LerougeS.Girard-LauriaultP. L. (2018). Plasma polymer films to regulate fibrinogen adsorption: effect of pressure and competition with human serum albumin. Plasma process. Polym.15, 1800040. 10.1002/ppap.201800040
20
BuhlK. B.AgergaardA. H.LillethorupM.NikolajsenJ. P.PedersenS. U.DaasbjergK. (2020). Polymer brush coating and adhesion technology at scale. Polym. (Basel)12, 1475. 10.3390/polym12071475
21
BurgessK. A.HuH. H.WagnerW. R.FederspielW. J. (2009). Towards microfabricated biohybrid artificial lung modules for chronic respiratory support. Biomed. Microdevices11, 117–127. 10.1007/s10544-008-9215-2
22
ButtarelloM.PlebaniM. (2008). Automated blood cell counts: state of the art. Am. J. Clin. Pathol.130, 104–116. 10.1309/EK3C7CTDKNVPXVTN
23
CarterS.-S. D.AtifA.-R.KadekarS.LanekoffI.EngqvistH.VargheseO. P.et al (2020). PDMS leaching and its implications for on-chip studies focusing on bone regeneration applications. Organs-on-a-Chip2, 100004. 10.1016/j.ooc.2020.100004
24
CastroD.PatilS. M.KeenaghanM. (2022). Arterial blood gas. Treasure Island, FL: StatPearls Publishing.
25
CasuB. (1985). Structure and biological activity of heparin. Adv. Carbohydr. Chem. Biochem.43, 51–134. 10.1016/S0065-2318(08)60067-0
26
ChenH.ChenY.SheardownH.BrookM. A. (2005). Immobilization of heparin on a silicone surface through a heterobifunctional PEG spacer. Biomaterials26, 7418–7424. 10.1016/j.biomaterials.2005.05.053
27
ChenS.LiL.ZhaoC.ZhengJ. (2010). Surface hydration: principles and applications toward low-fouling/nonfouling biomaterials. Polym. Guildf.51, 5283–5293. 10.1016/j.polymer.2010.08.022
28
ChungI.LipG. Y. H. (2003). Virchow’s triad revisited: blood constituents. Pathophysiol. Haemost. Thromb.33, 449–454. 10.1159/000083844
29
ComptonO. C.KimS.PierreC.TorkelsonJ. M.NguyenS. T. (2010). Crumpled graphene nanosheets as highly effective barrier property enhancers. Adv. Mat.22, 4759–4763. 10.1002/adma.201000960
30
ConvertL.ChabotV.ZermattenP. J.HamelR.CloarecJ. P.LecomteR.et al (2012). Passivation of KMPR microfluidic channels with bovine serum albumin (BSA) for improved hemocompatibility characterized with metal-clad waveguides. Sensors Actuators, B Chem.173, 447–454. 10.1016/j.snb.2012.07.061
31
ConveryN.GadegaardN. (2019). 30 Years of microfluidics. Micro Nano Eng.2, 76–91. 10.1016/j.mne.2019.01.003
32
DabaghiM.SaraeiN.FuschG.RochowN.BrashJ. L.FuschC.et al (2020). Microfluidic blood oxygenators with integrated hollow chambers for enhanced air exchange from all four sides. J. Memb. Sci.596, 117741. 10.1016/j.memsci.2019.117741
33
DaimonT.GotohY. (1982). Cytochemical evidence of the origin of the dense tubular system in the mouse platelet. Histochemistry76, 189–196. 10.1007/bf00501921
34
D’AmicoL.AjamiN. J.AdachiJ. A.GascoyneP. R. C.PetrosinoJ. F. (2017). Isolation and concentration of bacteria from blood using microfluidic membraneless dialysis and dielectrophoresis. Lab. Chip17, 1340–1348. 10.1039/c6lc01277a
35
De SomerF.ËoisK. F.Van OeverenW.PoelaertJ.De WolfD.EbelsT.et al (2000). Phosphorylcholine coating of extracorporeal circuits provides natural protection against blood activation by the material surface. Eur. J. Cardiothorac. Surg.18, 602–606. 10.1016/s1010-7940(00)00508-x
36
DevineR.GoudieM. J.SinghaP.SchmiedtC.DouglassM.BrisboisE. J.et al (2020). Mimicking the endothelium: dual action heparinized nitric oxide releasing surface. ACS Appl. Mat. Interfaces12, 20158–20171. 10.1021/acsami.9b22277
37
Díez-PascualA. M. (2022). PMMA-based nanocomposites for odontology applications: a state-of-the-art. Int. J. Mol. Sci.23, 10288. 10.3390/ijms231810288
38
DingY. H.FlorenM.TanW. (2016). Mussel-inspired polydopamine for bio-surface functionalization. Biosurface Biotribology2, 121–136. 10.1016/j.bsbt.2016.11.001
39
DuY. J.BerryL. R.ChanA. K. C. (2011). Chemical-physical characterization of polyurethane catheters modified with a novel antithrombin-heparin covalent complex. J. Biomater. Sci. Polym. Ed.22, 2277–2294. 10.1163/092050610X538227
40
DunkelbergerJ. R.SongW. C. (2010). Complement and its role in innate and adaptive immune responses. Cell Res.20, 34–50. 10.1038/cr.2009.139
41
EmersonM.MomiS.PaulW.AlbertiP. F.PageC.GreseleP. (1999). Endogenous nitric oxide acts as a natural antithrombotic agent in vivo by inhibiting platelet aggregation in the pulmonary vasculature. Thromb. Haemost.81, 961–966. 10.1055/s-0037-1614607
42
FallonB. P.Lautner-CsorbaO.ThompsonA. J.LautnerG.KaydenA.JohnsonM. D.et al (2022). A pumpless artificial lung without systemic anticoagulation: the Nitric Oxide Surface Anticoagulation system. J. Pediatr. Surg.57, 26–33. 10.1016/j.jpedsurg.2021.09.015
43
FanJ.LiS.WuZ.ChenZ. (2018). “Diffusion and mixing in microfluidic devices,” in Microfluidics for pharmaceutical applications (Elsevier Inc). 10.1016/B978-0-12-812659-2.00003-X
44
FeaugasT.NewmanG.CalzuolaS. T.DominguesA.ArditiW.PorriniC.et al (2023). Design of artificial vascular devices: hemodynamic evaluation of shear-induced thrombogenicity. Front. Mech. Eng.9, 1060580. 10.3389/fmech.2023.1060580
45
FischerM.MaitzM. F.WernerC. (2018). “7-Coatings for biomaterials to improve hemocompatibility,” in Hemocompatibility of biomaterials for clinical applications (Elsevier Ltd). 10.1016/B978-0-08-100497-5.00007-0
46
FlaumenhaftR.ShardaA. (2018). The life cycle of platelet granules. F1000Research7, 236. 10.12688/f1000research.13283.1
47
FlemingG.AveyardJ.FothergillJ. L.McBrideF.RavalR.D’SaR. A. (2017). Nitric oxide releasing polymeric coatings for the prevention of biofilm formation. Polym. (Basel)9, 601. 10.3390/polym9110601
48
FotovvatiB.NamdariN.DehghanghadikolaeiA. (2019). On coating techniques for surface protection: a review. J. Manuf. Mat. Process.3, 28. 10.3390/jmmp3010028
49
García-OrtizA.SerradorJ. M. (2018). Nitric oxide signaling in T cell-mediated immunity. Trends Mol. Med.24, 412–427. 10.1016/j.molmed.2018.02.002
50
GencturkE.MutluS.UlgenK. O. (2017). Advances in microfluidic devices made from thermoplastics used in cell biology and analyses. Biomicrofluidics11, 051502. 10.1063/1.4998604
51
Getinge (2018). Getinge Maquet. Available at: https://www.getinge.com/int/ (Accessed June 26, 2023).
52
GimbelA. A.HsiaoJ. C.KimE. S.LewisD. J.RisoleoT. F.UrbanJ. N.et al (2021). A high gas transfer efficiency microfluidic oxygenator for extracorporeal respiratory assist applications in critical care medicine. Artif. Organs45, E247–E264. 10.1111/aor.13935
53
GökaltunA.KangY. B.Abraham)YarmushM. L.UstaO. B.AsatekinA. (2019). Simple surface modification of poly(dimethylsiloxane) via surface segregating smart polymers for biomicrofluidics. Sci. Rep.9, 7377. 10.1038/s41598-019-43625-5
54
GokaltunA.YarmushM. L.AsatekinA.UstaO. B. (2017). Recent advances in nonbiofouling PDMS surface modification strategies applicable to microfluidic technology. Technol. Singap. World Sci.5, 1–12. 10.1142/s2339547817300013
55
Gómez-GrasG.AbadM. D.PérezM. A. (2021). Mechanical performance of 3D-printed biocompatible polycarbonate for biomechanical applications. Polym. (Basel)13, 3669. 10.3390/polym13213669
56
GrigioniM.MorbiducciU.D’AvenioG.Di BenedettoG.Del GaudioC. (2005). A novel formulation for blood trauma prediction by a modified power-law mathematical model. Biomech. Model. Mechanobiol.4, 249–260. 10.1007/s10237-005-0005-y
57
Guha ThakurtaS.SubramanianA. (2011). Evaluation of in situ albumin binding surfaces: a study of protein adsorption and platelet adhesion. J. Mat. Sci. Mat. Med.22, 137–149. 10.1007/s10856-010-4169-3
58
GusenbauerM.TóthováR.MazzaG.BrandlM.SchreflT.JančigováI.et al (2018). Cell damage index as computational indicator for blood cell activation and damage. Artif. Organs42, 746–755. 10.1111/aor.13111
59
HasanA.WaibhawG.PandeyL. M. (2018). Conformational and organizational insights into serum proteins during competitive adsorption on self-assembled monolayers. Langmuir34, 8178–8194. 10.1021/acs.langmuir.8b01110
60
Hassanpour-TamrinS.Sanati-NezhadA.SenA. (2021). A simple and low-cost approach for irreversible bonding of polymethylmethacrylate and polydimethylsiloxane at room temperature for high-pressure hybrid microfluidics. Sci. Rep.11, 4821. 10.1038/s41598-021-83011-8
61
HedayatiM.NeufeldM. J.ReynoldsM. M.KipperM. J. (2019). The quest for blood-compatible materials: recent advances and future technologies. Mat. Sci. Eng. R. Rep.138, 118–152. 10.1016/j.mser.2019.06.002
62
HeiF.GuanY.YuK. (2023). Extracorporeal life support. Singapore: Springer Nature.
63
HellmannA.KleinS.HesselmannF.DjeljadiniS.Schmitz-RodeT.JockenhoevelS.et al (2020). EndOxy: mid-term stability and shear stress resistance of endothelial cells on PDMS gas exchange membranes. Artif. Organs44, E419–E433. 10.1111/aor.13712
64
HeoY. S.CabreraL. M.SongJ. W.FutaiN.TungY. C.SmithG. D.et al (2007). Characterization and resolution of evaporation-mediated osmolality shifts that constrain microfluidic cell culture in poly(dimethylsiloxane) devices. Anal. Chem.79, 1126–1134. 10.1021/ac061990v
65
HeshC. A.QiuY.LamW. A. (2019). Vascularized microfluidics and the blood–endothelium interface. Nature388, 18–547. 10.3390/mi11010018
66
HilalT.MuddJ.DeLougheryT. G. (2019). Hemostatic complications associated with ventricular assist devices. Res. Pract. Thromb. Haemost.3, 589–598. 10.1002/rth2.12226
67
HongJ. K.WaterhouseA. (2023). Bioinspired approaches to engineer antithrombogenic medical devices for vascular intervention. Arterioscler. Thromb. Vasc. Biol.43, 797–812. 10.1161/ATVBAHA.122.318238
68
HorbettT. A. (2013). Adsorbed proteins on biomaterials. Third Ed. Elsevier. 10.1016/B978-0-08-087780-8.00036-X
69
HorbettT. A. (2018). Fibrinogen adsorption to biomaterials. J. Biomed. Mat. Res.106, 2777–2788. 10.1002/jbm.a.36460
70
HoshiaR. A.LithaR. V.JenaM. C.AllenJ. B.LapidosaK. A.AmeerG. (2013). The blood and vascular cell compatibility of heparin-modified ePTFE vascular grafts. Biomaterials34, 30–41. 10.1016/j.biomaterials.2012.09.046
71
HosseinnejadA.FischerT.JainP.BleilevensC.JakobF.SchwanebergU.et al (2021). Enzyme mimetic microgel coating for endogenous nitric oxide mediated inhibition of platelet activation. J. Colloid Interface Sci.601, 604–616. 10.1016/j.jcis.2021.05.143
72
HuC. C.LeeK. R.RuaanR. C.JeanY. C.LaiJ. Y. (2006). Gas separation properties in cyclic olefin copolymer membrane studied by positron annihilation, sorption, and gas permeation. J. Memb. Sci.274, 192–199. 10.1016/j.memsci.2005.05.034
73
HyltonD. M.ShalabyS. W.LatourR. A. (2005). Direct correlation between adsorption-induced changes in protein structure and platelet adhesion. J. Biomed. Mat. Res. - Part A73, 349–358. 10.1002/jbm.a.30295
74
IqbalM.DinhD. K.AbbasQ.ImranM.SattarH.Ul AhmadA. (2019). Controlled surface wettability by plasma polymer surface modification. Surfaces2, 349–371. 10.3390/surfaces2020026
75
IsraelachviliJ. (1997). The different faces of poly(ethylene glycol). Proc. Natl. Acad. Sci.94, 8378–8379. 10.1073/pnas.94.16.8378
76
JafferI. H.FredenburghJ. C.HirshJ.WeitzJ. I. (2015). Medical device-induced thrombosis: what causes it and how can we prevent it?J. Thromb. Haemost.13, S72–S81. 10.1111/jth.12961
77
JafferI. H.WeitzJ. I. (2019). The blood compatibility challenge. Part 1: blood-contacting medical devices: the scope of the problem. Acta Biomater.94, 2–10. 10.1016/j.actbio.2019.06.021
78
JanaS. (2019). Endothelialization of cardiovascular devices. Acta Biomater.99, 53–71. 10.1016/j.actbio.2019.08.042
79
JankowskiP.GarsteckiP. (2016). Stable hydrophilic surface of polycarbonate. Sensors Actuators, B Chem.226, 151–155. 10.1016/j.snb.2015.11.100
80
JensenM. J.PeelA.HorneR.ChamberlainJ.XuL.HansenM. R.et al (2021). Antifouling and mechanical properties of photografted zwitterionic hydrogel thin-film coatings depend on the cross-link density. ACS Biomater. Sci. Eng.7, 4494–4502. 10.1021/acsbiomaterials.1c00852
81
JeongH.ParkK.YooJ. C.HongJ. (2018). Structural heterogeneity in polymeric nitric oxide donor nanoblended coatings for controlled release behaviors. RSC Adv.8, 38792–38800. 10.1039/c8ra07707j
82
JiangB.GuoH.ChenD.ZhouM. (2022). Microscale investigation on the wettability and bonding mechanism of oxygen plasma-treated PDMS microfluidic chip. Appl. Surf. Sci.574, 151704. 10.1016/j.apsusc.2021.151704
83
KalathottukarenM. T.KizhakkedathuJ. N. (2018). “2-Mechanisms of blood coagulation in response to biomaterials: extrinsic factors,” in Hemocompatibility of biomaterials for clinical applications. Editor SiedleckiC. A. (Elsevier Ltd). 10.1016/B978-0-08-100497-5.00003-3
84
KamathS.BlannA. D.LipG. Y. H. (2001). Platelet activation: assessment and quantification. Eur. Heart J.22, 1561–1571. 10.1053/euhj.2000.2515
85
KanitthamniyomP.ZhangY. (2018). Application of polydopamine in biomedical microfluidic devices. Microfluid. Nanofluidics22, 24–13. 10.1007/s10404-018-2044-6
86
KehD.GerlachM.KürerI.SpielmannS.KernerT.BuschT.et al (1999). Nitric oxide diffusion across membrane lungs protects platelets during simulated extracorporeal circulation. Eur. J. Clin. Invest.29, 344–350. 10.1046/j.1365-2362.1999.00459.x
87
KhazanM.HdayatiM. (2014). The role of nitric oxide in health and diseases. Scimetr3, e87393. 10.5812/scimetr.20987
88
KhetaniS.YongK. W.Ozhukil KollathV.EastickE.AzarmaneshM.KaranK.et al (2020). Engineering shelf-stable coating for microfluidic organ-on-A-chip using bioinspired catecholamine polymers. ACS Appl. Mat. Interfaces12, 6910–6923. 10.1021/acsami.9b20826
89
KimS.YeS. H.AdamoA.OrizondoR. A.JoJ.ChoS. K.et al (2020). A biostable, anti-fouling zwitterionic polyurethane-urea based on PDMS for use in blood-contacting medical devices. J. Mat. Chem. B8, 8305–8314. 10.1039/d0tb01220c
90
KobayashiY. (2010). The regulatory role of nitric oxide in proinflammatory cytokine expression during the induction and resolution of inflammation. J. Leukoc. Biol.88, 1157–1162. 10.1189/jlb.0310149
91
KöhneI. (2020). Haemolysis induced by mechanical circulatory support devices: unsolved problems. Perfus. (United Kingdom)35, 474–483. 10.1177/0267659120931307
92
KolarM.MozetičM.Stana-KleinschekK.FröhlichM.TurkB.VeselA. (2015). Covalent binding of heparin to functionalized PET materials for improved haemocompatibility. Mater. (Basel)8, 1526–1544. 10.3390/ma8041526
93
KovachK. M.CapadonaJ. R.GuptaA. SenPotkayJ. A. (2014). The effects of PEG-based surface modification of PDMS microchannels on long-term hemocompatibility. J. Biomed. Mat. Res. - Part A102, 4195–4205. 10.1002/jbm.a.35090
94
KovachK. M.LabarberaM. A.MoyerM. C.CmolikB. L.Van LunterenE.Sen GuptaA.et al (2015). In vitro evaluation and in vivo demonstration of a biomimetic, hemocompatible, microfluidic artificial lung. Lab. Chip15, 1366–1375. 10.1039/c4lc01284d
95
KrajewskiS.NeumannB.KurzJ.PerleN.Avci-AdaliM.CattaneoG.et al (2015). Preclinical evaluation of the thrombogenicity and endothelialization of bare metal and surface-Coated neurovascular stents. Am. J. Neuroradiol.36, 133–139. 10.3174/ajnr.A4109
96
KrishnamoorthiR.AnbazhaganR.ThankachanD.Thuy DinhV. T.TsaiH. C.LaiJ. Y.et al (2023). Antiblood cell adhesion of mussel-inspired chondroitin sulfate- and caffeic acid-modified polycarbonate membranes. Langmuir39, 717–727. 10.1021/acs.langmuir.2c01688
97
KuchinkaJ.WillemsC.TelyshevD. V.GrothT. (2021). Control of blood coagulation by hemocompatible material surfaces—a review. Bioengineering8, 215–226. 10.3390/bioengineering8120215
98
KumarD. R.HanlinE. R.GlurichI.MazzaJ. J.YaleS. H. (2010). Virchow’s contribution to the understanding of thrombosis and cellular biology. Clin. Med. Res.8, 168–172. 10.3121/cmr.2009.866
99
LabarrereC. A.DabiriA. E.KassabG. S. (2020). Thrombogenic and inflammatory reactions to biomaterials in medical devices. Front. Bioeng. Biotechnol.8, 123. 10.3389/fbioe.2020.00123
100
LachauxJ.HwangG.AroucheN.NaserianS.HarouriA.LotitoV.et al (2021). A compact integrated microfluidic oxygenator with high gas exchange efficiency and compatibility for long-lasting endothelialization. Lab. Chip21, 4791–4804. 10.1039/d1lc00356a
101
LaiC. C.ChungC. K. (2020). Hydrophilicity and optic property of polyethylene glycol coating on polydimethylsiloxane for fast prototyping and its application to backlight microfluidic chip. Surf. Coatings Technol.389, 125606. 10.1016/j.surfcoat.2020.125606
102
LaiJ.SunderlandB.XueJ.YanS.ZhaoW.FolkardM.et al (2006). Study on hydrophilicity of polymer surfaces improved by plasma treatment. Appl. Surf. Sci.252, 3375–3379. 10.1016/j.apsusc.2005.05.038
103
LaiJ. Y.JienJ. M.LinS. H. (1993). Gas permeation in polycarbonate membranes prepared by the wet-phase inversion method. Chem. Eng. Sci.48, 4069–4074. 10.1016/0009-2509(93)80251-K
104
LarssonA.DérandH. (2002). Stability of polycarbonate and polystyrene surfaces after hydrophilization with high intensity oxygen RF plasma. J. Colloid Interface Sci.246, 214–221. 10.1006/jcis.2001.8032
105
LeckbandD.ShethS.HalperinA. (1999). Grafted poly(ethylene oxide) brushes as nonfouling surface coatings. J. Biomater. Sci. Polym. Ed.10, 1125–1147. 10.1163/156856299x00720
106
LeeH. A.MaY.ZhouF.HongS.LeeH. (2019). Material-independent surface chemistry beyond polydopamine coating. Acc. Chem. Res.52, 704–713. 10.1021/acs.accounts.8b00583
107
LeeJ. H.KimS. K.ParkH. H.KimT. S. (2015). TiO2 coated microfluidic devices for recoverable hydrophilic and hydrophobic patterns. J. Micromechanics Microengineering25, 035032. 10.1088/0960-1317/25/3/035032
108
LeeJ. K.KungH. H.MockrosL. F. (2008). Microchannel technologies for artificial lungs: (1) theory. ASAIO J.54, 372–382. 10.1097/MAT.0b013e31817ed9e1
109
LeeW. L.DowneyG. P. (2001). Leukocyte elastase: physiological functions and role in acute lung injury. Am. J. Respir. Crit. Care Med.164, 896–904. 10.1164/ajrccm.164.5.2103040
110
LeighB. L.ChengE.XuL.DerkA.HansenM. R.GuymonC. A. (2019). Antifouling photograftable zwitterionic coatings on PDMS substrates. Langmuir35, 1100–1110. 10.1021/acs.langmuir.8b00838
111
LeonardE. F.VromanL. (1992). Is the Vroman effect of importance in the interaction of blood with artificial materials?J. Biomater. Sci. Polym. Ed.3, 95–107. 10.1163/156856292X00105
112
LeungJ. M.BerryL. R.AtkinsonH. M.CorneliusR. M.SandejasD.RochowN.et al (2015). Surface modification of poly(dimethylsiloxane) with a covalent antithrombin-heparin complex for the prevention of thrombosis: use of polydopamine as bonding agent. J. Mat. Chem. B3, 6032–6036. 10.1039/c5tb00808e
113
LiL.YangL.LiaoY.YuH.LiangZ.ZhangB.et al (2020). Superhydrophilic versus normal polydopamine coating: a superior and robust platform for synergistic antibacterial and antithrombotic properties. Chem. Eng. J.402, 126196. 10.1016/j.cej.2020.126196
114
LillehojP. B.HoC. M. (2010). “A long-term, stable hydrophilic poly(dimethylsiloxane) coating for capillary-based pumping,” in Proc. IEEE Int. Conf. Micro Electro Mech. Syst., Hong Kong, China, 24-28 January 2010, 1063–1066. 10.1109/MEMSYS.2010.5442393
115
LinhardtR.MurugesanS.XieJ. (2008). Immobilization of heparin: approaches and applications. Curr. Top. Med. Chem.8, 80–100. 10.2174/156802608783378891
116
LiuQ.SinghaP.HandaH.LocklinJ. (2017). Covalent grafting of antifouling phosphorylcholine-based copolymers with antimicrobial nitric oxide releasing polymers to enhance infection-resistant properties of medical device coatings. Langmuir33, 13105–13113. 10.1021/acs.langmuir.7b02970
117
LiuY.AiK.LuL. (2014). Polydopamine and its derivative materials: synthesis and promising applications in energy, environmental, and biomedical fields. Chem. Rev.114, 5057–5115. 10.1021/cr400407a
118
LivaNova (2023). LivaNova. Available at: https://www.livanova.com/cardiopulmonary/en-us (Accessed June 26, 2023).
119
LongH. P.LaiC. C.ChungC. K. (2017). Polyethylene glycol coating for hydrophilicity enhancement of polydimethylsiloxane self-driven microfluidic chip. Surf. Coatings Technol.320, 315–319. 10.1016/j.surfcoat.2016.12.059
120
LowL. A.MummeryC.BerridgeB. R.AustinC. P.TagleD. A. (2021). Organs-on-chips: into the next decade. Nat. Rev.20, 345–361. 10.1038/s41573-020-0079-3
121
LoweG. D. O. (2003). Virchow’s triad revisited: abnormal flow. Pathophysiol. Haemost. Thromb.33, 455–457. 10.1159/000083845
122
LuoJ.FanJ. B.WangS. (2020). Recent progress of microfluidic devices for hemodialysis. Small16, 1904076. 10.1002/smll.201904076
123
LuoR.TangL.WangJ.ZhaoY.TuQ.WengY.et al (2013). Improved immobilization of biomolecules to quinone-rich polydopamine for efficient surface functionalization. Colloids Surfaces B Biointerfaces106, 66–73. 10.1016/j.colsurfb.2013.01.033
124
LuoR.ZhangJ.ZhuangW.DengL.LiL.YuH.et al (2018). Multifunctional coatings that mimic the endothelium: surface bound active heparin nanoparticles with: in situ generation of nitric oxide from nitrosothiols. J. Mat. Chem. B6, 5582–5595. 10.1039/c8tb00596f
125
LyuN.DuZ.QiuH.GaoP.YaoQ.XiongK.et al (2020). Mimicking the nitric oxide-releasing and glycocalyx functions of endothelium on vascular stent surfaces. Adv. Sci.7, 2002330. 10.1002/advs.202002330
126
Madhurakkat PerikamanaS. K.LeeJ.LeeY. B.ShinY. M.LeeE. J.MikosA. G.et al (2015). Materials from mussel-inspired chemistry for cell and tissue engineering applications. Biomacromolecules16, 2541–2555. 10.1021/acs.biomac.5b00852
127
MagoshiT.MatsudaT. (2002). Formation of polymerized mixed heparin/albumin surface layer and cellular adhesional responses. Biomacromolecules3, 976–983. 10.1021/bm0200377
128
MaulT. M.MassicotteM. P.WeardenP. D. (2016). “ECMO biocompatibility: surface coatings, anticoagulation, and coagulation monitoring,” in Extracorporeal membrane oxygenation: advances in therapy. Editor FirstenbergM. S. (Rijeka, Croatia: IntechOpen), 27–61. 10.5772/63888
129
McVerryB.PolaskoA.RaoE.HaghniazR.ChenD.HeN.et al (2022). A readily scalable, clinically demonstrated, antibiofouling zwitterionic surface treatment for implantable medical devices. Adv. Mat.34, 2200254. 10.1002/adma.202200254
130
Medtronic (2020). Balance™ biosurface. Available at: https://europe.medtronic.com/xd-en/healthcare-professionals/products/cardiovascular/cardiopulmonary/balance-biosurface.html (Accessed June 26, 2023).
131
MellgrenK.FribergL. G.MellgrenG.HednerT.WennmalmÅ.WadenvikH. (1996). Nitric oxide in the oxygenator sweep gas reduces platelet activation during experimental perfusion. Ann. Thorac. Surg.61, 1194–1198. 10.1016/0003-4975(96)00017-3
132
MercaderA.YeS. H.KimS.OrizondoR. A.ChoS. K.WagnerW. R. (2022). PDMS-zwitterionic hybrid for facile, antifouling microfluidic device fabrication. Langmuir38, 3775–3784. 10.1021/acs.langmuir.1c03375
133
MichanetzisG. P. A.KatsalaN.MissirlisY. F. (2003). Comparison of haemocompatibility improvement of four polymeric biomaterials by two heparinization techniques. Biomaterials24, 677–688. 10.1016/S0142-9612(02)00382-4
134
MirandaI.SouzaA.SousaP.RibeiroJ.CastanheiraE. M. S.LimaR.et al (2022). Properties and applications of PDMS for biomedical engineering: a review. J. Funct. Biomater.13, 2. 10.3390/jfb13010002
135
MondalA.SinghaP.DouglassM.EstesL.GarrenM.GriffinL.et al (2021). A synergistic new approach toward enhanced antibacterial efficacy via antimicrobial peptide immobilization on a nitric oxide-releasing surface. ACS Appl. Mat. Interfaces13, 43892–43903. 10.1021/acsami.1c08921
136
MukhopadhyayR. (2007). When PDMS isn’t the best. Anal. Chem.79, 3248–3253. 10.1021/ac071903e
137
NeubauerK.ZiegerB. (2021). Endothelial cells and coagulation. Cell Tissue Res.387, 391–398. 10.1007/s00441-021-03471-2
138
NieblerR. A.Chiang-ChingH.DaleyK.JaneckeR.JobeS. M.MitchellM. E.et al (2021). Nitric oxide added to the sweep gas of the oxygenator during cardiopulmonary bypass in infants: a pilot randomized controlled trial. Artif. Organs45, 22–28. 10.1111/aor.13788
139
NielsenJ. B.HansonR. L.AlmughamsiH. M.PangC.FishT. R.WoolleyA. T. (2020). Microfluidics: innovations in materials and their fabrication and functionalization. Anal. Chem.92, 150–168. 10.1021/acs.analchem.9b04986
140
OlanderB.WirsénA.AlbertssonA. C. (2003). Silicone elastomer surface functionalized with primary amines and subsequently coupled with heparin. Biomacromolecules4, 145–148. 10.1021/bm025654+
141
OliaS. E.MaulT. M.AntakiJ. F.KamenevaM. V. (2016). Mechanical blood trauma in assisted circulation: sublethal RBC damage preceding hemolysis. Int. J. Artif. Organs39, 150–159. 10.5301/ijao.5000478
142
OlssonP.LarmO. (1991). Biologically active heparin coating in medical devices. Int. J. Artif. Organs14, 453–456. 10.1177/039139889101400801
143
ÖzgüzarH. F.EvrenE.MeydanA. E.KabayG.GöçmenJ. S.BuyukserinF.et al (2022). Plasma-Assisted surface modification and heparin immobilization: dual-functionalized blood-contacting biomaterials with improved hemocompatibility and antibacterial features. Adv. Mat. Interfaces10, 2202009. 10.1002/admi.202202009
144
ParkJ. H.SutT. N.JackmanJ. A.FerhanA. R.YoonB. K.ChoN. J. (2017). Controlling adsorption and passivation properties of bovine serum albumin on silica surfaces by ionic strength modulation and cross-linking. Phys. Chem. Chem. Phys.19, 8854–8865. 10.1039/c7cp01310h
145
ParkK.KimS.JoY.ParkJ.KimI.HwangS.et al (2022). Lubricant skin on diverse biomaterials with complex shapes via polydopamine-mediated surface functionalization for biomedical applications. Bioact. Mater25, 555–568. 10.1016/j.bioactmat.2022.07.019
146
ParkK.MaoF. W.ParkH. (1991). The minimum surface fibrinogen concentration necessary for platelet activation on dimethyldichlorosilane‐coated glass. J. Biomed. Mat. Res.25, 407–420. 10.1002/jbm.820250311
147
PiconeP.SabatinoM. A.AjovalasitA.GiacomazzaD.DispenzaC.Di CarloM. (2019). Biocompatibility, hemocompatibility and antimicrobial properties of xyloglucan-based hydrogel film for wound healing application. Int. J. Biol. Macromol.121, 784–795. 10.1016/j.ijbiomac.2018.10.078
148
PituruS. M.GreabuM.TotanA.ImreM.PanteaM.SpinuT.et al (2020). A review on the biocompatibility of PMMA-Based dental materials for interim prosthetic restorations with a glimpse into their modern manufacturing techniques. Mater. (Basel)13, 2894. 10.3390/ma13132894
149
PlegueT. J.KovachK. M.ThompsonA. J.PotkayJ. A. (2018). Stability of polyethylene glycol and zwitterionic surface modifications in PDMS microfluidic flow chambers. Langmuir34, 492–502. 10.1021/acs.langmuir.7b03095
150
PorriniC.RamaraoN.TranS. L. (2020). Dr. NO and Mr. Toxic - the versatile role of nitric oxide. Biol. Chem.401, 547–572. 10.1515/hsz-2019-0368
151
PotkayJ. A. (2014). The promise of microfluidic artificial lungs. Lab. Chip14, 4122–4138. 10.1039/c4lc00828f
152
PrestonT. J.RatliffT. M.GomezD.OlshoveV. F.NicolK. K.SargelC. L.et al (2010). Modified surface coatings and their effect on drug adsorption within the extracorporeal life support circuit. J. Extra. Corpor. Technol.42, 199–202. 10.1051/ject/201042199
153
PrimcG. (2020). Recent advances in surface activation of polytetrafluoroethylene (PTFE) by gaseous plasma treatments. Polym. (Basel)12, 2295–2297. 10.3390/polym12102295
154
QiuH.QiP.LiuJ.YangY.TanX.XiaoY.et al (2019). Biomimetic engineering endothelium-like coating on cardiovascular stent through heparin and nitric oxide-generating compound synergistic modification strategy. Biomaterials207, 10–22. 10.1016/j.biomaterials.2019.03.033
155
RadomskiM. W.PalmerR. M. J.MoncadaS. (1987). Endogenous nitric oxide inhibits human platelet adhesion to vascular endothelium. Lancet330, 1057–1058. 10.1016/S0140-6736(87)91481-4
156
RecekN.MozeticM.JaganjacM.MilkovicL.ZarkovicN.VeselA. (2014). Adsorption of proteins and cell adhesion to plasma treated polymer substrates. Int. J. Polym. Mat. Polym. Biomater.63, 685–691. 10.1080/00914037.2013.854243
157
RegehrK. J.DomenechM.KoepselJ. T.CarverK. C.Ellison-ZelskiS. J.MurphyW. L.et al (2009). Biological implications of polydimethylsiloxane-based microfluidic cell culture. Lab. Chip9, 2132–2139. 10.1039/b903043c
158
RochowN.MananA.WuW. I.FuschG.MonkmanS.LeungJ.et al (2014). An integrated array of microfluidic oxygenators as a neonatal lung assist device: in vitro characterization and in vivo demonstration. Artif. Organs38, 856–866. 10.1111/aor.12269
159
RossidisA. C.LawrenceK. M.MejaddamA. Y.KimA. G.BaumgartenH. D.CoonsB. E.et al (2020). The effects of nitric oxide in oxygenator sweep gas during extracorporeal circulation in a neonatal ovine model. ASAIO J.66, 671–676. 10.1097/MAT.0000000000001047
160
RouxE.BougaranP.DufourcqP.CouffinhalT. (2020). Fluid shear stress sensing by the endothelial layer. Front. Physiol.11, 861. 10.3389/fphys.2020.00861
161
RoyE.GalasJ. C.VeresT. (2011). Thermoplastic elastomers for microfluidics: towards a high-throughput fabrication method of multilayered microfluidic devices. Lab. Chip11, 3193–3196. 10.1039/c1lc20251k
162
RoyE.PallandreA.HornyM. C.DelapierreF. D.HornyM. C.DelapierreF. D.et al (2016). “Overview of materials for microfluidic applications,” in Advances in microfluidics - new applications in biology, energy, and materials Sciences. Editor YuX. (Rijeka, Croatia: IntechOpen), 422.
163
RyuJ. H.MessersmithP. B.LeeH. (2018). Polydopamine surface chemistry: a decade of discovery. ACS Appl. Mat. Interfaces10, 7523–7540. 10.1021/acsami.7b19865
164
SadrearhamiZ.ShafieeF. N.HoK. K. K.KumarN.KrasowskaM.BlencoweA.et al (2019). Antibiofilm nitric oxide-releasing polydopamine coatings. ACS Appl. Mat. Interfaces11, 7320–7329. 10.1021/acsami.8b16853
165
SantosJ.VedulaE. M.LaiW.IsenbergB. C.LewisD. J.LangD.et al (2021). Toward development of a higher flow rate hemocompatible biomimetic microfluidic blood oxygenator. Micromachines12, 888. 10.3390/mi12080888
166
SchlenoffJ. B. (2014). Zwitteration: coating surfaces with zwitterionic functionality to reduce nonspecific adsorption. Langmuir30, 9625–9636. 10.1021/la500057j
167
SchrottW.SloukaZ.ČervenkaP.StonJ.NebylaM.PřibylM.et al (2009). Study on surface properties of PDMS microfluidic chips treated with albumin. Biomicrofluidics3, 44101. 10.1063/1.3243913
168
SeabraA. B.MartinsD.SimõesM. M. S. G.Da SilvaR.BrocchiM.De OliveiraM. G. (2010). Antibacterial nitric oxide-releasing polyester for the coating of blood-contacting artificial materials. Artif. Organs34, 204–214. 10.1111/j.1525-1594.2010.00998.x
169
ShakeriA.ImaniS. M.ChenE.YousefiH.ShabbirR.DidarT. F. (2019). Plasma-induced covalent immobilization and patterning of bioactive species in microfluidic devices. Lab. Chip19, 3104–3115. 10.1039/c9lc00364a
170
SharmaV.DhayalM.GovindShivaprasadS. M.JainS. C. (2007). Surface characterization of plasma-treated and PEG-grafted PDMS for micro fluidic applications. Vacuum81, 1094–1100. 10.1016/j.vacuum.2007.02.004
171
ShenB.XiongB.WuH. (2015). Convenient surface functionalization of whole-Teflon chips with polydopamine coating. Biomicrofluidics9, 044111. 10.1063/1.4927675
172
ShinD. A.LeeJ. C.ShinH.ChoY. J.KimH. C. (2021). Point-of-care testing of plasma free hemoglobin and hematocrit for mechanical circulatory support. Sci. Rep.11, 3788–3789. 10.1038/s41598-021-83327-5
173
SimmondsM. J.WatanabeN.NandakumarD.HorobinJ. (2018). “Blood-device interaction,” in Mechanical circulatory and respiratory support (Elsevier Inc). 10.1016/B978-0-12-810491-0.00019-9
174
Simon-WalkerR.RomeroR.StaverJ. M.ZangY.ReynoldsM. M.PopatK. C.et al (2017). Glycocalyx-inspired nitric oxide-releasing surfaces reduce platelet adhesion and activation on titanium. ACS Biomater. Sci. Eng.3, 68–77. 10.1021/acsbiomaterials.6b00572
175
SinM. C.ChenS. H.ChangY. (2014). Hemocompatibility of zwitterionic interfaces and membranes. Polym. J.46, 436–443. 10.1038/pj.2014.46
176
SivakumarR.LeeN. Y. (2020). Microfluidic device fabrication mediated by surface chemical bonding. Analyst145, 4096–4110. 10.1039/d0an00614a
177
SivaramanB.LatourR. A. (2010). The relationship between platelet adhesion on surfaces and the structure versus the amount of adsorbed fibrinogen. Biomaterials31, 832–839. 10.1016/j.biomaterials.2009.10.008
178
SkogbyM.FribergL. G.AdrianK.MellgrenK. (2003). Pharmacological inhibition of plasma coagulation and platelet activation during experimental long-term perfusion. Scand. Cardiovasc. J.37, 222–228. 10.1080/14017430310002185
179
StaufferF. (2014). La préparation d’émulsions doubles par un système microfluidique. Available at: https://hal.univ-lorraine.fr/hal-01732016/document.
180
SundriyalP.PandeyM.BhattacharyaS. (2020). Plasma-assisted surface alteration of industrial polymers for improved adhesive bonding. Int. J. Adhes. Adhes.101, 102626. 10.1016/j.ijadhadh.2020.102626
181
Sweryda-KrawiecB.DevarajH.JacobG.HickmanJ. J. (2004). A new interpretation of serum albumin surface passivation. Langmuir20, 2054–2056. 10.1021/la034870g
182
SzydzikC.BrazilekR. J.NesbittW. S. (2020). A review of design considerations for hemocompatibility within microfluidic systems. Semin. Thromb. Hemost.46, 622–636. 10.1055/s-0040-1710340
183
TanS. H.NguyenN. T.ChuaY. C.KangT. G. (2010). Oxygen plasma treatment for reducing hydrophobicity of a sealed polydimethylsiloxane microchannel. Biomicrofluidics4, 32204–32208. 10.1063/1.3466882
184
TanX.GaoP.LiY.QiP.LiuJ.ShenR.et al (2021). Poly-dopamine, poly-levodopa, and poly-norepinephrine coatings: comparison of physico-chemical and biological properties with focus on the application for blood-contacting devices. Bioact. Mat.6, 285–296. 10.1016/j.bioactmat.2020.06.024
185
TeliguiL.DalmayracE.MabilleauG.MacchiL.GodonA.CorbeauJ. J.et al (2014). An ex vivo evaluation of blood coagulation and thromboresistance of two extracorporeal circuit coatings with reduced and full heparin dose. Interact. Cardiovasc. Thorac. Surg.18, 763–769. 10.1093/icvts/ivu011
186
TemizY.LovchikR. D.KaigalaG. V.DelamarcheE. (2015). Lab-on-a-chip devices: how to close and plug the lab?Microelectron. Eng.132, 156–175. 10.1016/J.MEE.2014.10.013
187
Terumo (2018). Xcoating™ surface coating. Available at: https://www.terumocv.com/doc/876640_Xcoating-Brochure_JULY2018_FINAL_LowRes.pdf (Accessed June 26, 2023).
188
ThomasS. G. (2019). The structure of resting and activated platelets. 4th ed.Elsevier Inc. 10.1016/B978-0-12-813456-6.00003-5
189
ThompsonA. J.MaL. J.MajorT.JeakleM.Lautner-CsorbaO.GoudieM. J.et al (2020). Assessing and improving the biocompatibility of microfluidic artificial lungs. Acta Biomater.112, 190–201. 10.1016/j.actbio.2020.05.008
190
ThonJ. N.DykstraB. J.BeaulieuL. M. (2017). Platelet bioreactor: accelerated evolution of design and manufacture. Platelets28, 472–477. 10.1080/09537104.2016.1265922
191
TousoulisD.KampoliA.-M.Tentolouris Nikolaos PapageorgiouC.StefanadisC. (2011). The role of nitric oxide on endothelial function. Curr. Vasc. Pharmacol.10, 4–18. 10.2174/157016112798829760
192
TrantidouT.ElaniY.ParsonsE.CesO. (2017). Hydrophilic surface modification of pdms for droplet microfluidics using a simple, quick, and robust method via pva deposition. Microsystems Nanoeng.3, 16091. 10.1038/micronano.2016.91
193
TsaiW. B.GrunkemeierJ. M.HorbettT. A. (1999). Human plasma fibrinogen adsorption and platelet adhesion to polystyrene. J. Biomed. Mat. Res.44, 130–139. 10.1002/(SICI)1097-4636(199902)44:2<130::AID-JBM2>3.0.CO;2-9
194
TsaoC. W.DeVoeD. L. (2009). Bonding of thermoplastic polymer microfluidics. Microfluid. Nanofluidics6, 1–16. 10.1007/s10404-008-0361-x
195
TsaoC. W. (2016). Polymer microfluidics: simple, low-cost fabrication process bridging academic lab research to commercialized production. Micromachines7, 225. 10.3390/mi7120225
196
Van MidwoudP. M.JanseA.MeremaM. T.GroothuisG. M. M.VerpoorteE. (2012). Comparison of biocompatibility and adsorption properties of different plastics for advanced microfluidic cell and tissue culture models. Anal. Chem.84, 3938–3944. 10.1021/ac300771z
197
Van OeverenW.HaanJ.LagermanP.SchoenP. (2002). Comparison of coagulation activity tests in vitro for selected biomaterials. Artif. Organs26, 506–511. 10.1046/j.1525-1594.2002.06872.x
198
VaughnM. W.KuoL.LiaoJ. C. (1998). Estimation of nitric oxide production and reaction rates in tissue by use of a mathematical model. Am. J. Physiol.274, H2163–H2176. 10.1152/ajpheart.1998.274.6.H2163
199
VeselA.MozeticM.JaganjacM.MilkovicL.CipakA.ZarkovicN. (2011). Biocompatibility of oxygen-plasma-treated polystyrene substrates. EPJ Appl. Phys.56, 24024–24027. 10.1051/epjap/2011110169
200
VictorA.RibeiroJ.AraújoF. F. (2019). Study of PDMS characterization and its applications in biomedicine: a review. J. Mech. Eng. Biomech.4, 1–9. 10.24243/jmeb/4.1.163
201
VirchowR. (1856). Gesammelte Abhandlungen zur Wissenschaftlichen Medicin. Frankfurt am Main, Germany: Meidinger.
202
VoicuD.LestariG.WangY.DeBonoM.SeoM.ChoS.et al (2017). Thermoplastic microfluidic devices for targeted chemical and biological applications. RSC Adv.7, 2884–2889. 10.1039/c6ra27592c
203
WagnerM. S.CastnerD. G. (2004). Analysis of adsorbed proteins by static time-of-flight secondary ion mass spectrometry. Appl. Surf. Sci.231–232, 366–376. 10.1016/j.apsusc.2004.03.100
204
WangP. G.XianM.TangX.WuX.WenZ.CaiT.et al (2002). Nitric oxide donors: chemical activities and biological applications. Chem. Rev.102, 1091–1134. 10.1021/cr000040l
205
WeberM.SteinleH.GolombekS.HannL.SchlensakC.WendelH. P.et al (2018). Blood-contacting biomaterials: in vitro evaluation of the hemocompatibility. Front. Bioeng. Biotechnol.6, 99. 10.3389/fbioe.2018.00099
206
Wei HouH.GanH. Y.BhagatA. A. S.LiL. D.LimC. T.HanJ. (2012). A microfluidics approach towards high-throughput pathogen removal from blood using margination. Biomicrofluidics6, 24115–2411513. 10.1063/1.4710992
207
WeiQ.BechererT.Angioletti-UbertiS.DzubiellaJ.WischkeC.NeffeA. T.et al (2014). Protein interactions with polymer coatings and biomaterials. Angew. Chem. - Int. Ed.53, 8004–8031. 10.1002/anie.201400546
208
WellerR. B. (2009). Nitric oxide-containing nanoparticles as an antimicrobial agent and enhancer of wound healing. J. Invest. Dermatol.129, 2335–2337. 10.1038/jid.2009.149
209
WillersA.ArensJ.MarianiS.PelsH.MaessenJ. G.HackengT. M.et al (2021). New trends, advantages and disadvantages in anticoagulation and coating methods used in extracorporeal life support devices. Membr. (Basel)11, 617. 10.3390/membranes11080617
210
WilliamsD. F. (2008). On the mechanisms of biocompatibility. Biomaterials29, 2941–2953. 10.1016/j.biomaterials.2008.04.023
211
WilsonC. J.CleggR. E.LeavesleyD. I.PearcyM. J. (2005). Mediation of biomaterial-cell interactions by adsorbed proteins: a review. Tissue Eng.11, 1–18. 10.1089/ten.2005.11.1
212
WolbergA. S.AlemanM. M.LeidermanK.MachlusK. R. (2012). Procoagulant activity in hemostasis and thrombosis: virchow’s triad revisited. Anesth. Analg.114, 275–285. 10.1213/ANE.0b013e31823a088c
213
WongI.HoC. M. (2009). Surface molecular property modifications for poly(dimethylsiloxane) (PDMS) based microfluidic devices. Microfluid. Nanofluidics7, 291–306. 10.1007/s10404-009-0443-4
214
WuB.GerlitzB.GrinnellB. W.MeyerhoffM. E. (2007a). Polymeric coatings that mimic the endothelium: combining nitric oxide release with surface-bound active thrombomodulin and heparin. Biomaterials28, 4047–4055. 10.1016/j.biomaterials.2007.06.002
215
WuY.ZhouZ.MeyerhoffM. E. (2007b). In vitro platelet adhesion on polymeric surfaces with varying fluxes of continuous nitric oxide release. J. Biomed. Mat. Res. Part A81A, 956–963. 10.1002/jbm.a.31105
216
XiaN.MayC. J.McArthurS. L.CastnerD. G. (2002). Time-of-Flight secondary ion mass spectrometry analysis of conformational changes in adsorbed protein films. Langmuir18, 4090–4097. 10.1021/la020022u
217
YamazoeH.OyaneA.NashimaT.ItoA. (2010). Reduced platelet adhesion and blood coagulation on cross-linked albumin films. Mat. Sci. Eng. C30, 812–816. 10.1016/j.msec.2010.03.015
218
YangZ.TuQ.ZhuY.LuoR.LiX.XieY.et al (2012). Mussel-inspired coating of polydopamine directs endothelial and smooth muscle cell fate for re-endothelialization of vascular devices. Adv. Healthc. Mat.1, 548–559. 10.1002/adhm.201200073
219
YangZ.YangY.XiongK.LiX.QiP.TuQ.et al (2015). Nitric oxide producing coating mimicking endothelium function for multifunctional vascular stents. Biomaterials63, 80–92. 10.1016/j.biomaterials.2015.06.016
220
YeW.ShiQ.HouJ.GaoJ.LiC.JinJ.et al (2015). Fabricating bio-inspired micro/nano-particles by polydopamine coating and surface interactions with blood platelets. Appl. Surf. Sci.351, 236–242. 10.1016/j.apsusc.2015.05.108
221
YehP. Y.ZhangZ.LinM.CaoX. (2012). Nonfouling hydrophilic poly(ethylene glycol) engraftment strategy for PDMS/SU-8 heterogeneous microfluidic devices. Langmuir28, 16227–16236. 10.1021/la303196m
222
YoonT.MoonH. S.SongJ. W.HyunK. A.JungH. Il (2019). Automatically controlled microfluidic system for continuous separation of rare bacteria from blood. Cytom. Part A95, 1135–1144. 10.1002/cyto.a.23909
223
YuH.ChongZ. Z.TorS. B.LiuE.LohN. H. (2015). Low temperature and deformation-free bonding of PMMA microfluidic devices with stable hydrophilicity via oxygen plasma treatment and PVA coating. RSC Adv.5, 8377–8388. 10.1039/c4ra12771d
224
ZahidA.DaiB.HongR.ZhangD. (2017). Optical properties study of silicone polymer PDMS substrate surfaces modified by plasma treatment. Mat. Res. Express4, 105301–105308. 10.1088/2053-1591/aa8645
225
ZelzerM.AlbuttD.AlexanderM. R.RussellN. A. (2012). The role of albumin and fibronectin in the adhesion of fibroblasts to plasma polymer surfaces. Plasma process. Polym.9, 149–156. 10.1002/ppap.201100054
226
ZhangC.JinJ.ZhaoJ.JiangW.YinJ. (2013). Functionalized polypropylene non-woven fabric membrane with bovine serum albumin and its hemocompatibility enhancement. Colloids Surfaces B Biointerfaces102, 45–52. 10.1016/j.colsurfb.2012.08.007
227
ZhangL.CaseyB.GalanakisD. K.MarmoratC.SkoogS.VorvolakosK.et al (2017). The influence of surface chemistry on adsorbed fibrinogen conformation, orientation, fiber formation and platelet adhesion. Acta Biomater.54, 164–174. 10.1016/j.actbio.2017.03.002
228
ZhangM.PaulsJ. P.BartnikowskiN.HaymetA. B.ChanC. H. H.SuenJ. Y.et al (2021). Anti-thrombogenic surface coatings for extracorporeal membrane oxygenation: a narrative review. ACS Biomater. Sci. Eng.7, 4402–4419. 10.1021/acsbiomaterials.1c00758
229
ZhouJ.KhodakovD. A.EllisA. V.VoelckerN. H. (2012). Surface modification for PDMS-based microfluidic devices. Electrophoresis33, 89–104. 10.1002/elps.201100482
Summary
Keywords
haemocompatibility, microfluidics, surface modification, coating, medical devices, thrombosis, biomaterials
Citation
Newman G, Leclerc A, Arditi W, Calzuola ST, Feaugas T, Roy E, Perrault CM, Porrini C and Bechelany M (2023) Challenge of material haemocompatibility for microfluidic blood-contacting applications. Front. Bioeng. Biotechnol. 11:1249753. doi: 10.3389/fbioe.2023.1249753
Received
29 June 2023
Accepted
07 August 2023
Published
17 August 2023
Volume
11 - 2023
Edited by
Meng Tian, Sichuan University, China
Reviewed by
Rui Zhong, Chinese Academy of Medical Sciences and Peking Union Medical College, China
Zeng He, Hospital of Chengdu Office of People’s Government of Tibetan Autonomous Region, China
Updates
Copyright
© 2023 Newman, Leclerc, Arditi, Calzuola, Feaugas, Roy, Perrault, Porrini and Bechelany.
This is an open-access article distributed under the terms of the Creative Commons Attribution License (CC BY). The use, distribution or reproduction in other forums is permitted, provided the original author(s) and the copyright owner(s) are credited and that the original publication in this journal is cited, in accordance with accepted academic practice. No use, distribution or reproduction is permitted which does not comply with these terms.
*Correspondence: Gwenyth Newman, g.newman@campus.unimib.it
†These authors have contributed equally to this work and share last authorship
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