Blood pressure in the Greenland shark as estimated from ventral aortic elasticity Free

Among lower vertebrates, including fishes, the degree of aerobic activity is reflected by the level of pressure generated by the heart. For example, tunas have high metabolic rates and are fast, continuous swimmers compared with other fishes such as trout or carp (Randall, 1970; Bernal et al., 2001; Brill and Lai, 2016). Not surprisingly, ventral aortic blood pressure in tunas (∼12 kPa; Bushnell and Brill, 1992; Jones et al., 2005) is more than three times higher than that in trout, approaching levels found in mammals (∼13 kPa; McDonald, 1974). Some sharks (e.g. catsharks) have relatively low activity, metabolic rate and blood pressure (3–5 kPa; Taylor et al., 1977), while others (e.g. lamnid sharks) have higher metabolism and blood pressure (>7 kPa; Lai et al., 1997) and the ability to swim fast.

Greenland sharks (Somniosus microcephalus) live in deep, cold water in high northern latitudes, grow to a large size (>5 m), have a lifespan of hundreds of years (Hansen, 1963; Nielsen et al., 2016) and appear to be very sluggish with little capacity for sustained high-speed swimming (Compagno et al., 2005; Watanabe et al., 2012; Nielsen et al., 2016). Although one of the largest extant marine fish, knowledge of their life history, ecology and physiology is very limited (MacNeil et al., 2012; Herbert et al., 2017; Costantini et al., 2017). There are virtually no in vivo measurements of physiological parameters from this species, because of the difficulty of obtaining and handling specimens. Field studies using accelerometers reveal very slow sustained swim speeds (<0.2 body length s⁻¹), with tail beat frequencies of the order of only a few per minute (Skomal and Benz, 2004; Watanabe et al., 2012). Based on all these features, we expected blood pressure in S. microcephalus to be relatively low compared with that of other sharks, even species considered to have low levels of swimming activity such as catsharks.

In animals with closed circulatory systems, the major arteries act as an elastic reservoir, storing blood transiently when the ventricle contracts, and providing flow while the heart refills. Elastic recoil of the artery wall converts the pulsatile output of the heart into smoother flow in the periphery. In fish, the heart pumps blood to the gills through a highly compliant and elastic ventral aorta (VA). Studies have shown that the proximal aortas of vertebrates and some invertebrates all have non-linear inflation curves. Commonly, the aorta is very compliant at low pressures but changes fairly abruptly to a stiff-walled vessel at higher pressures. Because of cylindrical geometry, this non-linear behaviour is necessary to prevent aneurysms, or pressure ruptures (Shadwick, 1999), and the transition in compliance typically occurs at about the mean blood pressure of each species (Fig. 1A; Roach and Burton, 1957; Gosline, 2018). This inherent elastic property provides a method to estimate mean blood pressure, and has been used for animals in which in vivo measurements are not available or are intractable (Gosline and Shadwick, 1982; Shadwick, 1995).

A variation of this method was developed for teleosts (Jones et al., 2005) using the bulbus arteriosus, an elastic chamber that connects the ventricle to the VA (Priede, 1976; Bushnell et al., 1992; Braun et al., 2003a,b). Jones et al. (2005) validated their method by showing good accord (R²=0.89) between measured blood pressures and predictions from the inflation properties of the bulbi of 10 species.

The elastic properties of the aortic wall arise from the combined effect of two distinct fibrous proteins, elastin and collagen. Elastin is highly extensible with a tensile stiffness (or elastic modulus) about equal to that of natural rubber (∼1 MPa) while collagen is 1000 times stiffer (∼1 GPa) and relatively inextensible. Compliance is initially associated with the high extensibility of elastin fibres that bear wall tension until distension of the artery is great enough to unfold and recruit the collagen fibres, resulting in a rapid increase in wall stiffness with pressure (Roach and Burton, 1957; Lillie et al., 2012). The ratio of collagen to elastin provides an index of wall stiffness at physiological pressures in different species, but the total quantity and structural arrangement of the connective tissue fractions are also important in determining the artery mechanical properties – in particular, its distensibility as a function of pressure. A consequence of this adaptation is that, while the elastic modulus (stiffness) increases sharply with radial expansion, a value of 0.3–0.5 MPa is consistently observed for the aorta at mean physiological pressure in a wide range of species (Gibbons and Shadwick, 1989; Shadwick, 1999). This observation provides a second method to estimate blood pressure from tissue mechanics.

The purpose of our study, then, was to estimate mean blood pressure in the Greenland shark from measurements of the elastic properties of the VA.

VAs were collected post-mortem from six Greenland sharks, S. microcephalus (Bloch and J. G. Schneider 1801), that were captured by long-line fishing in Greenland waters during two research cruises (2012, 2017) under permits from Greenland Home Rule (2017-9208). Animals ranged in size from 2.64 to 3.7 m total length, with body masses of approximately 170 to 700 kg.

Each VA was dissected free from adventitia and separated from the heart by sectioning at the outflow of the conus arteriosus, and from the gill complex by sectioning the afferent branchial vessels. During dissection, it was apparent that the VA was very elastic as there was significant recoil when the vessel was excised (average shortening measured ex vivo versus in situ of 38±7%). Next, a large cannula was inserted into the vessel proximal to the conus arteriosus and tied in with silk suture, and a smaller one was fitted to the distal outflow in the same manner (Fig. 1B) along with a side arm to a calibrated pressure transducer. This left a relatively uniform segment 6–8 cm in length between gill afferent vessels 3 and 4 where VA diameter could be monitored upon inflation (Fig. 1B). Before inflation, the VA segment was extended longitudinally and held to restore its in vivo length.

Inflation tests were conducted by filling the VA with 4°C shark saline (Driedzic and Gesser, 1988) from a reservoir that was slowly hoisted over a pulley suspended from the ceiling. Before taking measurements, the VA was preloaded through several inflation cycles to approximately 6 kPa. Pressure was monitored continuously by reading the DC voltage output of the amplified pressure transducer signal with a voltmeter. During the inflations, a video recording was made that included the VA and also the voltmeter. This allowed frame by frame determination of inflation pressure (P) and the corresponding VA external diameter (D). The latter was measured using ImageJ on video frames that were selected as the closest to a pressure series of 0 to 5 kPa in increments of 0.5 kPa. Then, each D value was divided by the zero-pressure D to give a diameter ratio.

Following the inflation trials, a short ring was sliced from the VA at the location where D had been measured; this was turned on end and photographed in order to determine wall thickness (h), using ImageJ. This value represents the thickness of the unpressurized, unstretched vessel wall. Ring D averaged 1.27±0.19 cm with an average h of 0.15±0.03 cm. Based on the longitudinal stretch needed to restore in vivo length, h for the stretched vessel was first calculated at P=0, and then at each selected inflation P, based on the corresponding D and assuming constant volume of the vessel wall tissue (Shadwick and Gosline, 1985). From this, the internal radius (r) at each P increment was calculated. Then, circumferential wall stress was calculated as P×r/h, and circumferential wall strain was calculated as the increment in mean wall radius divided by its initial value, where mean wall radius was r+h/2. Stress and strain increments were then used to calculate the stiffness, or incremental elastic modulus, of the VA as a function of inflation P (eqns 1–3 and 12 of Shadwick and Gosline, 1985).

The artery wall structure was investigated by routine histological methods. Tissues were fixed in 4% formaldehyde buffered with filtered seawater, dehydrated through an ethanol series, embedded in wax and sectioned at 5 µm. Sections were stained for connective tissue (collagen in pink; elastin in black) by the Verhoff–van Gieson method, and viewed and photographed on a Zeiss Axio-Imager.A1 photomicroscope fitted with a Hitachi HV-F22 digital camera. Determinations of the relative elastin content were made by converting histological images of transverse and longitudinal sections to grayscale, then binary format using ImageJ software. With this method, elastin remains as black (grayscale value=255) while the rest of the colours are subtracted, leaving only white (grayscale value=0). By finding the average grayscale value for each image we could calculate the fraction of pixels that were black, and thus the proportion of the section area that was occupied by elastin. For comparison, a VA obtained from a short-fin mako shark (Isurus oxyrinchus, ∼70 kg body mass) was prepared and analysed in the same manner. Results are reported as means±s.d.

Our first method of blood pressure estimation was based on inflation data for six Greenland shark VAs (Fig. 2A) showing the expected non-linear increase in P versus D. It is notable how readily the VA expands at very low pressures (i.e. <2 kPa) before stiffening as pressure exceeds 2 kPa. Linear regressions are shown in Fig. 2A for the first five and last five data points. Their intersection marks the transition from compliant to stiff regions and defines the level that we regard as resting aortic blood pressure, as demonstrated previously for other animals (Roach and Burton, 1957). Here, this occurred at approximately 2.3 kPa.

An alternative estimation of blood pressure was based on the elastic modulus of the VA wall. Fig. 2B shows that the circumferential elastic modulus increases as a non-linear function of P, rising 100-fold between a P of 0.5 kPa and 4 kPa. Fig. 2C shows plots of the elastic modulus of the aorta from various vertebrates and invertebrates with closed circulatory systems versus P, normalized to the known mean blood pressure (P_mean) of each species (Shadwick, 1999). While these species have greatly varying levels of blood pressure, the normalized data show, remarkably, that the aortic elastic modulus is consistently 0.3–0.5 MPa at mean blood pressure in all species. If we assume this observation holds for the Greenland shark, then taking an average modulus of 0.4 MPa, we predict a mean blood pressure of 2.8 KPa in this species (Fig. 2B).

Combining the results from the two methods predicts a mean ventral aortic blood pressure for S. microcephalus of 2.3–2.8 kPa. We believe this is lower than blood pressures observed in any other elasmobranch, and fits with the expectations that this species is slow moving and has a relatively low aerobic metabolism (MacNeil et al., 2012; Watanabe et al., 2012). For comparison, in vivo studies report ventral aortic blood pressures from slow swimming sharks of 3.9 and 5.3 kPa (epaulette shark, Hemiscyllium ocellatum: Speers-Roesch et al., 2012; and catshark, Scyliorhinus canicula: Taylor et al., 1977, respectively), from more active species of 5.1–6.8 kPa (black-tipped reef shark, Carcharhinus melanoptera: Davie et al., 1993; and leopard shark, Triakis semifasciata: Lai et al., 1990), and from fast swimming sharks of >7 kPa (short-fin mako sharks, Isurus oxyrinchus: Lai et al., 1997). As in other fishes, there is undoubtedly a significant pressure drop across the gills due to resistance, such that the dorsal aortic pressure will be even lower than we predict for the VA. In teleosts and other sharks, this is typically a pressure decrease of about 25% (Stevens and Randall, 1967; Taylor et al., 1977; Stensløkken et al., 2004), suggesting that the systemic blood pressure in the Greenland shark may be below 2 kPa.

The organization of the load-bearing fibrous connective tissues in the VA of S. microcephalus should reflect its observed capacity to inflate to a higher degree at lower pressures than other species. Histological features bear this out. The VA wall in S. microcephalus is composed primarily of collagen, elastin and smooth muscle cells (Fig. 3A), organized in three distinct layers (intima, media, adventitia), reminiscent of what is seen in other vertebrate arteries (Shadwick, 1998, 1999). At the luminal surface, the intima comprises an endothelial cell layer supported by an internal elastic lamina (Fig. 3B,C). The media contains elastin fibres, smooth muscle cells and collagen fibres, while the adventitia is predominately loose collagen with scattered elastin fibres. An interesting feature of the media is a region about 50 µm thick adjacent to the intima where elastin fibres and muscle cells are oriented parallel to the longitudinal vessel axis, whereas elastin and muscle cells in much of the rest of the media are oriented circumferentially. This can be seen by comparing longitudinal and circumferential sections in Fig. 3B,C, and sagittal sections in Fig. 3E,F. This biaxial deposition of elastic fibres will provide resistance to stretching in both axes during pressurization in vivo.

In S. microcephalus, the elastin complement is much more dispersed than in the aorta of other vertebrate species, including other fishes (Satchell, 1971; Rhodin, 1972; Gibbons and Shadwick, 1989; Braun et al., 2003a; Fig. 3D). In transverse, longitudinal and sagittal sections, elastin is seen as fibres of 1–2 µm or less in diameter (Fig. 3B,C) rather than the fenestrated circumferential sheets seen in mammalian arteries (Wong and Langille, 1996; Clarke et al., 2015). This relatively loose connectivity of the fibres should allow a higher distensibility at low pressures compared with the mammalian arrangement (Gibbons and Shadwick, 1989). We determined that the area occupied by elastin in transverse and longitudinal sections averaged 27±2.5%. As a proxy for the volume fraction, this is about half of what is typical in mammalian aortas (Harkness et al., 1957; Roach and Burton, 1957). In a pressurized cylinder, circumferential wall tension is P×r. If the tension up to mean blood pressure is resisted by the elastin component, then the wall extensibility at a given pressure will be relatively higher when elastin is low in abundance and loosely linked, as in S. microcephalus. Conversely, in species with higher blood pressures, because of the greater density and connectivity of elastin fibres in the aortic walls, higher pressures will be required to achieve the same aortic distension. Above the inflection point of the P–D curve, collagen straightens and becomes the load-bearing element in all cases (recall collagen is 1000 times stiffer than elastin). Thus, the distribution and organization of the connective tissues is the primary structural mechanism whereby the aorta of different species have similar functional properties across a wide range of species-specific blood pressures (Fig. 2C). Remarkably, this pattern is also seen in the aorta of invertebrates with closed circulatory systems, such as cephalopods and crustaceans, where elastin analogues occur with collagen (Davison et al., 1995; McConnell et al., 1996; Shadwick, 1995, 1999; Shadwick and Gosline, 1981; Shadwick et al., 1990). These observations suggest that cellular control of the deposition of collagen and elastic fibre components may be related to the level of pressure experienced during growth and development of the circulatory system, specific to each species.

For comparison with S. microcephalus, we analysed a VA from the highly active short-fin mako shark. In this case, the VA wall has a much denser complement of elastin fibres (Fig. 3D) with an average elastin area of 53±2.6%, about double that of S. microcephalus, and its mean blood pressure (ca. 7 kPa) is substantially higher (Lai et al., 1997).

In this study, we used two methods to estimate the ventral aortic blood pressure of the enigmatic Greenland shark, based on artery wall mechanics. Together, these yielded predictions of 2.3–2.8 kPa, much lower than that of other shark species in which blood pressure has been measured. This low value for arterial pressure is not unexpected, considering the apparent low level of aerobic activity observed in this species, and this prediction is supported by the microscopic arrangement of elastin and collagen in the VA wall.

We thank the crews of RV Dana and RV Sanna for accommodating our research activities, Dr M. Lillie for valuable comments on the manuscript, and Dr A. W. Vogl for help with microscopy.