## SUMMARY

Vascular networks refer here mainly to the microscale capillary networks of the vascular system of mammals, although they may also be considered to include the small arteries that feed the capillaries and the small veins that drain them. The modeling of these networks for resting mammals is reviewed within the context of describing related scaling laws for mammals of vastly different size. Basic processes are considered and alternative approaches mentioned. All lead to the same scaling laws for the radius, length and number of the vessels. The applicability of the relations is illustrated using existing measurements. Discussion is also included on the effect of strenuous exercise on the scaling law for number of capillary vessels and matters related to it.

## Introduction

The general subject of this review is the modeling of the microscopic vascular (capillary) networks in animals, with attention directed specifically to mammals. The modeling to be dealt with is that associated with the derivation and discussion of `scaling laws' for these networks for mammals of vastly different size. For reviews of the basic concepts see also Dawson (1991, 2001, 2003). Experimental measurements on the scaling of the vascular networks of mammals have been reported by Schmidt-Nielsen and Pennycuik (1961), Gehr et al. (1981), and Hoppeler et al. (1981).

Scaling laws of the kind to be considered here are important in the general understanding of the vascular and cardiovascular system. If found appropriate, such scaling laws can illustrate that these systems all follow the same general pattern. Hence, the study of these systems on the basis of measurements from, say, the mouse can then reveal important information for the human, as well as other mammals.

### Broad features of the vascular system

The vascular system of mammals consists of two major parts: the systemic part associated with transport of blood to the body and the pulmonary part associated with transport of blood to the lungs. The architecture is basically the same for both parts. The systemic vascular system, for example, consists of the aorta, carrying oxygenated blood directly from the left side of the heart, and the smaller vessels branching from it. The latter lead ultimately to the capillary networks spread throughout the body. These vascular networks consist of very small arteries (the arterioles) that take blood to the capillaries, the capillaries themselves, through which exchange of products with the tissues occurs, and then the very small veins (the venules) that take blood away from the capillaries and ultimately return it to the right side of the heart for circulation in the pulmonary system for discharge of unwanted gaseous products and for recharge of oxygen in the blood. The flow system is illustrated in Fig. 1 (from Dawson, 1991). Attention here will be directed mainly towards the systemic system, although some reference will also be made to the pulmonary system, as appropriate.

## Modeling and scaling of the vascular networks

The systemic vascular networks of mammals consist of some 10-100 capillaries in each network. In muscle tissue, there are also reserve capillaries that open with exercise and provide increased blood flow, as first shown by Krogh (1920). This matter will be dealt with later; but for now, resting conditions will be assumed.

Each network may be considered to have its capillaries in parallel
arrangement. Within each, viscous resistance to blood flow dominates over
inertial resistance, because of the very small dimensions involved.
Considering all the many vascular networks on the systemic side of the
circulation, the net blood-pressure loss, Δ*P*, across them is
therefore described by the famous Hagen-Poiseuille equation for flow in small
vessels (Hagen, 1839;
Poiseuille, 1840), which may
be written as:
(1)
where μ denotes the viscosity coefficient of the blood,
*R*_{C}, *L*_{C} and *N*_{C}
denote `characteristic' (or typical) radius, length and number of capillaries,
respectively, and *Q*_{B} denotes cardiac output, that is, the
volume of blood ejected by the heart into the systemic vascular system over
the time of a heart beat.

The blood pressures in the vascular system of resting mammals are all essentially the same, as demonstrated many years ago by measurements of Gregg et al. (1937), and Woodbury and Hamilton (1937). The pressure drop across the vascular networks may similarly be assumed to be independent of mammal size. The blood viscosity is likewise known to be independent of mammal size (Amin and Sirs, 1985), and the cardiac output is known to be proportional to the product of heart rate and mammal mass (Holt et al., 1968). The following proportional relation may therefore be written from Equation (1): (2)

where ω denotes heart rate, *M*_{b} denotes mammal
mass (with *M*_{b}^{0} denoting no dependence on it),
and where the symbol α denotes proportionality.

In addition to this relation, another may be written associated with the fact that the total blood volume in mammals varies directly with mammal mass, as shown by Brody (1945). The total blood volume in the capillary system, as part of the whole, can therefore similarly be assumed to vary in this manner. The following relation results: (3)

Direct evidence for the latter relation exists for the pulmonary
capillaries (Gehr et al.,
1981) and there is no reason to expect differently for the
systemic capillaries. Relations (2) and (3) thus provide two relations, backed
by measurement, between the four unknown quantities *R*_{C},
*L*_{C}, *N*_{C} and ω. Two additional
relations are thus needed to complete the description. These may either be
empirical or theoretical. The latter is first considered. The following
discussion of these relations is based on earlier work by the author
(Dawson, 1991).

### Additional relations

The variables associated directly with the `characteristic' capillary
system of resting mammals can be expected to apply to the capillaries of any
organ of the body. There is, in fact, some evidence for this in the case of
the lungs, the kidneys and the muscles, as will be discussed later. Thus, the
number of capillaries in the heart may be assumed to be proportional to the
number of capillaries *N*_{C} associated with the relations (2)
and (3). The number of cardiac cells in the heart can also be considered to be
proportional to the number of capillaries supplying them. The volume of a
single cardiac cell can therefore be expected to be proportional to the ratio
of heart mass to capillary number; or, since heart mass and body mass are
proportional (Brody, 1945),
the volume of a single cardiac cell can be considered proportional to the
ratio *M*_{b}/*N*_{C}. The characteristic length
*d* of a cell is therefore expressible as
(4)

assuming all dimensions scale the same, like in fact the dimensions of the heart, which all scale as mammal mass to the power 1/3 (Dawson, 1991, 2001).

Now, cardiac tissue consists mainly of contraction fibers which, when
excited, provide the pumping action of the heart. The fibers consist of series
connections of small cardiac cells, separated by membranes. Contraction is
initiated in the upper heart and spreads over the heart through progressive
influx of ions into the cardiac cells, making the fibers contract. The
required two relations follow from consideration of the resting heart rate as
determined by the diameter of the cardiac fibers, with the latter assumed the
same as the linear dimension *d* defined above; and from consideration
of the influx of ions into the fibers.

The contraction (propagation) speed in cardiac fiber is assumed, like nerve
fiber, to be expressible as a power-law relation with fiber diameter; that is,
as *d*^{b} where `b' denotes a constant. Based on experimental
studies with isolated nerve fibers (generally considered analogous to heart
fiber), a value of `b' can be expected to be between 0.5 and 1.0
(Jack et al., 1975). A value
of `b' equal to 2/3 was determined appropriate previously
(Dawson, 1991). Now, the
period between heartbeats may reasonably be assumed to be proportional, under
change of scale, to the ratio of heart length (proportional to mammal mass to
the power 1/3) to contraction speed; and the heart rate must thus be equal to
the reciprocal of this period. The following relation, therefore, results from
these considerations (Dawson,
1991):
(5)

A second relation follows from consideration of the diffusion-like transfer
of ions into the cardiac cells over a period of heartbeat. The mass,
*m*, of ionic substance diffusing into (or out of) a cardiac cell can
be expected to depend on the dimension, *d*, of the cell, the diffusion
coefficient *D* (units of area per time), the concentration differenceΔ
*C* (units of mass per volume) between concentrations outside
and inside the cell, and the heart rate ω (units of reciprocal time).
The relation for *m* may be written in dimensionless form (so as to be
independent of particular units), as
(6)

where *f*(-) denotes a general function. The left-hand side of this
equation, with concentration difference Δ*C* assumed scale
invariant, is proportional to the diffusion mass per unit cell volume, and
this may be expected to be independent of mammal size. With the diffusion
constant *D* also scale invariant, as expected, it can be seen that the
product of heart rate and square of cell dimension must likewise be constant
under change of scale. Thus, heart rate is predicted to be inversely
proportional to the square of the heart-cell dimensions. Using the definition
of cardiac cell dimension of relation (4), the follow relation results
(Dawson, 1991):
(7)

As may be confirmed with simple algebra of proportions, relations (2) and (3), together with the two expressions of relations (5) and (7), provide the solution for the scaling laws for the characteristic capillary vessels in the form: (8a) (8b) (8c)

The scaling relation for the resting heart rate is also determined from the relations and that for cardiac output from its previously noted connection with heart rate, that is, (9a) (9b)

Experimental evidence for the relation for heart rate has existed for many years (Rihl, 1926; Clark, 1927). More recent work by Holt et al. (1968) provides experimental support for both the heart-rate and cardiac-output relations.

It is worthwhile to note the differences that arise if different values of `b' are used for the exponent in the above contraction-speed relation leading to relation (5). For the lower value of 0.5, the equations predict that heart rate should vary with mammal mass to a power of -4/15, that is, a power of about -0.27; and that the cardiac output should vary with mammal mass to a power of 11/15, that is, a power of about 0.73. For the higher value of 1, the equations predict an exponent value for heart rate of -2/9, that is, a power of -0.22; and that for cardiac output of 7/9, that is, a power of about 0.78. The differences are not especially significant, and for either choice of exponent `b', the relations for heart rate and cardiac output, if determined experimentally, could reasonably be rounded to the exponent values of -1/4 and 3/4, respectively.

The value of 2/3 for the exponent `b' in the contraction-speed relation, noted in connection with relation (5), was chosen earlier by the author (Dawson, 1991) because it led to the relations for cardiac output and heart rate, as generally accepted. Interestingly, if an extreme value for `b' of zero is assumed, the resulting expressions are that heart rate varies as mammal mass to the power -1/3 and that cardiac output varies with mammal mass to the power 2/3. The latter is unlikely, based in part on the work of Holt et al. (1968).

In addition to showing that the scaling laws for the capillary networks, as
well as the scaling laws for cardiac output and heart rate, can be determined
from fundamental considerations, it has been illustrated here that heart rate
varies inversely as the square of the diameter of the cardiac contraction
fibers. The latter offers an explanation (and the only one that I am aware of)
as to how and why the resting heart rate of, say, the mouse is many times that
of the human; that is, about 600 beats min^{-1} for mouse and about 60
beats min^{-1} for human.

Additional means for obtaining the above scaling laws have been considered earlier and involved use of empirical relations for heart rate (reciprocal 1/4 power relation) and oxygen consumption rate (3/4 power relation), as described by Dawson (2001, 2003). This approach leads to the same scaling laws as relations (8a-c).

### Some measurements

It may first be noted that direct experimental measurements are limited regarding the systemic side of the circulation, but the data available are consistent with the theory described here. In particular, there are the counting measurements of Kunkel (1930) for number of nephrons in the kidneys of mammals of various sizes. The nephron is the basic unit in the kidney and consists of a collection of capillary vessels. The number of capillaries per nephron can be expected to be the same for any mammal, and hence a count of nephrons in a kidney can be expected to be proportional to a count of capillaries in the kidney. The measurements of Kunkel (mouse to ox range) were analyzed by Adolph (1949) and shown to obey a power law relation, with mammal mass raised to the power 0.62, which may also be taken as 5/8, in agreement with relation (8c).

There are also measurements of Kunkel (1930) concerning the diameter of renal capsules of the nephrons that indicate variation with mammal mass to a power of essentially 1/12 (Adolph, 1949). This variation may be taken as evidence for the scaling relation for relation (8a), since the diameter of the renal capsules can be expected to be proportional to the radius of the contained capillaries within them.

In addition, there are measurements of rate of urine output of resting
mammals (mouse to elephant range) that indicate variation with mammal mass to
a power of essentially 5/6, as noted by Adolph
(1949). Net fluid flow from the
capillaries in the kidneys, insofar as scaling is concerned, can be expected
to be proportional to the product of capillary number *N*_{C}
and capillary length *L*_{C} as discussed earlier by the author
(Dawson, 1991). Relations
(8b,c) provide, in fact, the scaling exponent 5/6.

Finally, on the systemic side, there are measurements of capillary density in muscles by Schmidt-Nielsen and Pennycuik (1961) that presumably apply to the resting state, as considered here. Capillary spacing in resting muscle can be expected to be proportional to capillary radius, and capillary density can therefore be expected to be inversely proportional to the square of capillary radius; that is, as mammal mass to the power -1/6, based on relation (8a). The relation just described was recently confirmed from theoretical considerations (Dawson, 2003). The measurements of Schmidt-Nielsen and Pennycuik (bat to pig range) support this variation as illustrated in Fig. 2 for capillary density in the masseter (jaw) muscle of mammals. Similar agreement exists for measurements of Schmidt-Nielsen and Pennycuik (1961) regarding resting capillary density in the gastrocnemius (leg) muscle of mammals (Dawson, 2003).

For the pulmonary side of the circulation, measurements exist for capillary
volume and surface area (Gehr et al.,
1981). These data (shrew to cow range) may be used to obtain data
for capillary radius and net capillary length
(Dawson, 1991). Typical values
for the capillary radius are shown in Fig.
3 and support predictions from relation (8a). In average terms,
the volume of the capillaries was found by Gehr et al.
(1981) to be directly
proportional to mammal mass, and their surface area was found proportional to
mammal mass raised to about the power 0.93 (average of two sets of data).
These results imply that capillary radius *R*_{C} and net
capillary length *N*_{C}*L*_{C} scale with
mammal mass to powers 0.07 and 0.86, respectively, in good agreement with the
theoretical value from relations (8a-c) of 0.08 and 0.83.

The basic scaling relations (8a-c) may also be derived by replacing the two theoretical relations (5) and (7) by the empirical relation for heart rate, and either of the above experimentally confirmed relations for capillary number and capillary radius.

## Oxygen consumption rate

Among the many biological processes involved with the vascular networks, the most important is perhaps the transfer of oxygen from the blood to the surrounding tissues. The resting oxygen consumption rate of mammals (mouse to elephant range) is known to obey an average power-law relation with mammal mass raised to the power 3/4 (Kleiber, 1932; Brody and Procter, 1932; Brody, 1945). This relation applies over a wide range of mammal size, but, insofar as empirical relations are concerned, may be subject to modification for smaller mammals (Bartels, 1982; Heusner, 1991; Dodds et al., 2001). Interestingly, the careful work of Bishop (1999) on mammals and birds indicates no such deviations.

The oxygen consumption rate is considered in terms of the rate of oxygen
transfer *V̇*_{O2} across the
capillaries. This is described by the diffusion equation:
(10)

where *P*_{0} denotes the oxygen pressure in the blood,
*P*_{1} denotes the oxygen pressure immediately outside the
capillary, and *H*_{C} denotes the wall thickness of the
capillaries. Now, as discussed in earlier work
(Dawson, 2003), plausible
assumptions can be made that the ratios
*P*_{1}/*P*_{0} and
*R*_{C}/*H*_{C} are relatively independent of
mammal size, at least when a wide range of mammal size is considered. In
particular, the first ratio can be expected to be relatively independent of
scale since a change in oxygen pressure in the blood is likely to be
accompanied by a corresponding change in oxygen pressure in surrounding
tissue. The second ratio can be expected to be constant, or nearly so, in
order to maintain similar stress in the capillary walls from the
scale-invariant blood pressure. Variations from either of these assumptions
over a small range of size may, of course, account for deviations from the
average mentioned above. Adopting the assumptions, relation (10) reduces to
the expression:
(11)

Moreover, as already known (Dawson,
1991) on the basis of measurements by Schmidt-Nielsen and Larimer
(1958), the oxygen pressure
*P*_{0} in the blood can be considered to be proportional to
mammal mass to the power -1/12 (mouse to mule range). This correlation is
illustrated in Fig. 4, together
with an additional measurement for the elephant
(Bartels et al., 1963). With
the product *N*_{C}*L*_{C} varying with mammal
mass to the power 5/6, as required by relations (8a-c), the oxygen transfer
rate is thus seen to vary with mammal mass to the power 3/4, in accordance
with measurements over a broad range on mammal size.

It may be noted (at least within the writer's limited understanding) that `constructal theory', based in part on the assumption that vascular formation is an optimized flow architecture, also provides the power 3/4 for resting oxygen consumption rate (Bejan, 1997, 2000).

## Application of theory to drug therapy

A practical application of capillary scaling involves consideration of therapeutic drug concentrations in the blood of small mammals as they relate to humans. A specific example is provided by the chemotherapy drug methotrexate, which is a widely used (non-metabolized) drug in the treatment of cancer. Dedrick et al. (1970) showed that data from various mammals could be consolidated into a broad correlation by plotting the ratio of drug concentration in the blood to initial dose as a function of time since injection, when the latter was divided by mammal mass raised to the power 1/4. Since the blood-circulation time is proportional to mammal mass to the power 1/4 (Dawson, 1991), the resulting time scale is simply proportional to circulation time. It may be anticipated that some refinement could be gained by including the capillary geometry and scaling into the correlation.

The drug is assumed to be injected on the systemic venous side in a relatively short period of time. On passing through a general capillary, the classical view (Guyton, 1971) is that the blood initially expels some water and drug to surrounding tissue (Starling, 1896; Pappenheimer et al., 1951). Near the end of the capillary blood flow, some of the mixed drug is reabsorbed (see Fig. 5; from Dawson, 1991). Of course, in the event of fluctuating osmotic pressure, some capillary exchange, back and forth, could be expected along the entire length of the capillary.

In either case, a simplified process may be assumed for scaling purposes where the entire drug is removed by the capillaries during the initial cycle and some of the drug reabsorbed. In this case, the drug concentration at the injection site, after the initial cycle, will equal the amount reabsorbed. This process would perhaps lead to a reduced concentration at the site, compared with the actual process. However the same percentage difference may be expected (for a non-metabolized drug) for all mammals so that scaling is still possible in the present case.

The concentration of drug, *C* (in units of mass per volume of
blood), in the blood after the first complete cycle of blood circulation in
the above-simplified process will be proportional to the net volume of drug
reabsorbed per unit volume of blood. Flow into and out of capillaries can be
considered for scaling purposes (Dawson,
1991) to be proportional to a scale-independent constant and the
net capillary length, that is, *BN*_{C}*L*_{C},
where *B* denotes the filtration-absorption constant (units of area per
time). The concentration of drug reabsorbed over the time, *T*, for a
complete circulation is thus proportional, for scale-independent initial
concentration, to the ratio
*N*_{C}*L*_{C}*T*/*V*_{B},
where *V*_{B} denotes total blood volume. For any arbitrary
initial drug concentration *D*_{0}, the ratio is
*D*_{0}
*N*_{C}*L*_{C}/*V*_{B})*T*.

With additional cycles of blood circulation treated in the same way, the
effective initial dosage would (after the manner of
Dedrick et al. 1970) be
reduced by the factor *f*(*t*/*T*), where *f*(-)
denotes an unspecified function. Thus, concentration of drug in the blood at
any time, *t*, is described for scaling purposes by the relation:
(12)

Now, if the ratio *t*/*T* is fixed, the ratio on the
left-hand side of this relation will be proportional to the first ratio on the
right. The product *N*_{C}*L*_{C} varies with
mammal mass to the power 5/6, as indicated by relations (8a-c), the total
blood volume *V*_{B} varies directly with mammal mass
(Brody, 1945), and the time
for circulation *T* varies as mammal mass to the power 1/4, as
indicated previously. The desired scaling relations may be written, for
example, for the human relative to a smaller (or larger) mammal as
(13a)
(13b)

where subscripts `H' and `M' denotes values for the human and mammal, respectively.

Fig. 6 illustrates application of this scaling law in projecting measurements from the mouse (mass of 0.022 kg) to the human (mass of 70 kg) for the plasma concentration of methotrexate in the blood as a function of time. The basic measurements for the mouse, as used in developing the results of Fig. 6, are due to Dedrick et al. (1970) and the data for the human are due to Henderson et al. (1965). The solid curve shown in Fig. 6 is a simple `best-fit' power-law expression for comparison purposes.

The agreement of the scaled data from the mouse with that of the human, as
shown in Fig. 6, is indeed very
good. The factor
(*M*_{H}/*M*_{M})^{1/12} in the scaling
relation (13a) represents the effect of capillary process and is equal to
1.96. Without this factor, the predictions from the mouse would thus be
reduced by a factor of about 2. Overall, the factor can be seen to improve the
predictions over what they would be otherwise.

## Effects of strenuous exercise of mammals

An interesting aspect of the work in the present discussion is that the scaling laws for the radius and length of the capillaries forming the vascular networks can be determined on the basis of the resting condition of mammals. This aspect has been noted earlier (Dawson, 2003). Since the size of the capillaries cannot change with exercise, there can only be one set of scaling laws for these, and resting conditions provide these laws. Of course, resting conditions also provide the scaling laws for resting heart rate, cardiac output and oxygen consumption rate, as illustrated here.

For a number of years, it was generally thought that all scaling relations associated with the physiological functions of mammals (for example, cardiac output, oxygen consumption rate and heart rate) were the same for both resting and exercise states. This could be the case if such physiological variables increased during exercise by the same factor for all mammals. This would change the proportional factor in the scaling relations, but leave the scaling exponents with body mass unchanged. This is now known not to be the case, as a result of work by Baudinette (1978), Taylor et al. (1981), Weibel et al. (1991) and Bishop (1997, 1999), among others.

In particular, the oxygen consumption rate of mammals (bat to steer range) in strenuous exercise has been shown by Bishop (1999), in careful analysis of existing data, to vary with mammal mass raised to the power 0.88, that is, a power of about 7/8. This result is consistent with earlier work of Weibel et al. (1991) and the more recent work of Weibel et al. (2004). The power 7/8 is also consistent with `constructal theory' and the assumption that flow systems survive by forming easier access to the required flow (Bejan, 2000).

On the capillary scale, allowance appears to be made for exercise by increased activity of the capillary network through openings of reserve capillaries in the muscles (Krogh, 1920). This will change the scaling law for operative number of capillaries in the body, but will leave the scaling laws for dimensions of the capillaries unchanged. This view is, perhaps, consistent with the principle of `symmorphosis' (Taylor and Weibel, 1981; Weibel et al., 1991; Hoppeler and Weibel, 1998) requiring (in simple terms) that nothing more be provided in the design of mammals than that required for their purposes.

In terms of the present work, the new condition for scaling of the average capillary number is a modified form of relation (11) such that (14)

where *N*_{C}* ^{*}* denotes the modified
capillary number for exercise. With

*P*

_{0}and

*L*

_{C}varying, as in the resting state, with mammal mass to the powers -1/12 and 5/24, respectively, and maximum oxygen consumption rate varying with mammal mass to the power 7/8, it can be seen that the scaling relation for the modified capillary number is (15)

This relation corresponds to a `weighted' average for scaling of the number of capillaries in the body. The concept of a weighted average is consistent with recent discussion by Weibel (2002) and work of Darveau et al. (2002) on the rate of oxygen consumption during exercise. When compared with the resting state, with capillary number proportional to mammal mass to the power 5/8, the implication is that the ratio of average capillary number in strenuous exercise to resting number increases in proportion to mammal mass to the power 1/8. Perhaps gravity enters here in that larger mammals have to work harder than small mammals in overcoming their weight (as opposed to their mass) in exercise.

Of course, with strenuous exercise, resting-state similarity in the physiological response of mammals is lost. With fixed scaling of radius and length dimensions of the capillaries, it is impossible to satisfy all the earlier relations required for similar response among resting mammals. In this regard, capillary density in muscles that includes both resting and reserve capillaries (for strenuous exercise) cannot be expected to follow the simple scaling law noted earlier where resting capillary density varies with mammal mass to the power -1/6. This observation is consistent with sophisticated measurements of Hoppeler et al. (1981), which presumably detected both active and inactive capillaries as discussed recently (Dawson, 2003).

In spite of the loss of resting-state similarity in exercise, it is worthwhile to note that cardiac output in strenuous exercise appears to vary in the same way as oxygen consumption rate (Bishop, 1997), namely as mammal mass to the power 7/8. In this case, the pressure drop across capillary networks is still scale invariant like in the resting state, as can be seen from Equation (1). The rate at which energy is dissipated by viscous (frictional) resistance in the capillaries is proportional to the product of pressure drop and cardiac output. Considering all the capillary networks, this can then be seen to be proportional to the rate of oxygen supply to the body and, in particular, also to the heart since heart mass and body mass are proportional. A similar situation exists for the resting state. The ratio of rate of energy dissipation in capillary blood flow to rate of oxygen (fuel) supply to the heart is thus invariant with scale for both exercise and resting, consistent with good design practice.

This last matter may perhaps have implications regarding work by West et al. (1997), Banavar et al. (1999) and Dodds et al. (2001) on the efficiency of the design of the vascular networks of mammals. It may also have relevance in constructing a general basis for similarity in the strenuous-exercise state that provides, for example, the 7/8ths power law for oxygen-consumption rate, like that provided here for the 3/4-law for the resting state.

## Concluding remarks

Modeling of the vascular networks of mammals has been reviewed here, with the expressed goal of discussing relevant scaling laws for resting mammals of vastly different size. Both geometry and process have been considered. Results have been shown to be in good agreement with measurements for a wide range of mammal sizes. A main conclusion to be drawn from this review is that similarity exists for the vascular networks of mammals, as well as for related physiological processes.

Overall, the design of the vascular networks of mammals appears to be the same, with predictable adjustments for scale for resting mammals and some additional adjustment for exercise. An interesting question that presents itself is why the design follows essentially the same pattern for all mammals. The answer would appear to be simply because it is the `best' pattern, all things considered. In this regard, it has been noted that, for both resting and strenuous exercise, the rate of energy dissipation in blood flow in the vascular capillary networks appears to be proportional under change of scale to the oxygen rate supplied to the heart. The ratio of the two is thus invariant under change of scale for both resting and exercise.

## ACKNOWLEDGEMENTS

I am grateful to the referees for their valuable comments and criticisms of the original manuscript.

- © The Company of Biologists Limited 2005