The aim of this study was to compare physiological effects of hindlimb suspension (HLS) in tail‐ and pelvic‐HLS rat models to determine if severe stretch in the tail‐HLS rats lumbosacral skeleton may contribute to the changes traditionally attributed to simulated microgravity and musculoskeletal disuse in the tail‐HLS model. Adult male Sprague‐Dawley rats divided into suspended and control‐nonsuspended groups were subjected to two separate methods of suspension and maintained with regular food and water for 2 weeks. Body weights, food and water consumption, soleus muscle weight, tibial bone mineral density, random plasma insulin, and hindlimb pain on pressure threshold (PPT) were measured. X‐ray analysis demonstrated severe lordosis in tail‐ but not pelvic‐HLS animals. However, growth retardation, food consumption, and soleus muscle weight and tibial bone density (decreased relative to control) did not differ between two HLS models. Furthermore, HLS rats developed similar levels of insulinopenia and mechanical hyperalgesia (decreased PPT) in both tail‐ and pelvic‐HLS groups. In the rat‐to‐rat comparisons, the growth retardation and the decreased PPT observed in HLS‐rats was most associated with insulinopenia. In conclusion, these data suggest that HLS results in mild prediabetic state with some signs of pressure hyperalgesia, but lumbosacral skeleton stretch plays little role, if any, in these pathological changes.
- Hindlimb unloading
- pressure hyperalgesia
Hindlimb suspension (HLS) of rodents by the tail is a well‐established approach to create a ground‐based model of microgravity and musculoskeletal disuse that mimics many of the physiological changes associated with space flight, as well as with prolonged bed rest (Morey‐Holton and Globus 2002; Morey‐Holton et al. 2005; Carpenter et al. 2010). Among the most well‐characterized changes in HLS rodents are the bone and muscle atrophy that are universally experienced by astronauts during space missions and by bed‐ridden patients (Morey‐Holton and Globus 2002; Graebe et al. 2004).
Tail‐HLS in rodents is also a potential model for studies of another important effect of microgravity and disuse, specifically the development of a mild prediabetic state that is characterized by subclinical decrease in insulin secretion and loss of peripheral tissue sensitivity to insulin (Vernikos‐Danellis et al. 1976; Stuart et al. 1988; Leach et al. 1991; Mikines et al. 1991; Tobin et al. 2002; Graebe et al. 2004). Within 1–2 weeks of tail‐HLS, rats have been shown to develop insulinopenia (Nichols et al. 2008), insulin resistance and compensatory hyperinsulinemia (Stuart et al. 1993), or an increase in skeletal muscle insulin sensitivity (Henriksen et al. 1986; O'keefe et al. 2004). Although controversial, these observations warrant further exploration, as they may be critical for explaining limb disuse associated with bone loss as well as muscle atrophy (Stuart et al. 1993; Tischler et al. 1997; Thrailkill et al. 2005b; Fluckey et al. 2006; Wang et al. 2006). In addition, decreased insulin regulatory control has been linked to the development of muscle and visceral hyperalgesia in rat models of STZ‐induced prediabetes (Romanovsky et al. 2010) and muscle pain in tail‐HLS rats (Chowdhury et al. 2011). These problems may be related to both the back pain and gastrointestinal problems reported by a majority of astronauts and bed‐ridden human patients (Styf et al. 2001). Furthermore, understanding limb immobilization‐induced mechanical hyperalgesia in humans and animals (Hirose et al. 2001; Terkelsen et al. 2008; Ohmichi et al. 2012; Trierweiler et al. 2012), and pathogenesis of bone fracture and neuropathy risks in diabetes (Dobretsov et al. 2007; Leslie et al. 2007) provide additional rationale for this study.
Considering the nature of nociceptive changes in tail‐HLS rats, we first tested the physical consequences of stretching the lumbosacral section of the spine during tail‐HLS. Spine sprain and its associated injuries is one of most common causes of back pain in hospital admissions (Andersson 2008). Lengthening of gravity unloaded spinal columns and associated stretch of spinal roots have been discussed as a reason of low back pain in astronauts (Hutchinson et al. 1993; Styf et al. 2001; Carpenter et al. 2010). Signs of radiating low back pain were also described in SPARC‐null mice model of lumbar intervertebral disc degeneration (Millecamps et al. 2012). Similarly the lumbosacral stretch of the spinal column is a likely contributor to the pathogenic picture in tail‐HLS rat model of simulated microgravity. Whether this condition has any impact (affecting the pain and stress levels and possibly neurotrophic regulation) on the other major endpoints of hindlimb disuse in this model remain uncertain.
Therefore, the major focus of this work was to compare the effects of tail‐HLS with those of a model that is less stressful on the lumbar spine, namely the model in which the hindlimbs are suspended at the pelvis by a belt, termed pelvic‐HLS. We specifically compared these two HLS models with respect to their general stress levels (weight gain, daily water, and food intake), their pain on pressure threshold (PPT), of the extent of musculoskeletal atrophy and their plasma insulin levels following HLS, as a measure of pancreatic function.
Materials and Methods
All animal protocols were approved by Institutional Animal Care and Use committee and experiments were conducted in accord with the National Institute of Health Guide for the Care and Use of Laboratory Animals. Young adult male Sprague‐Dawley rats (200–250 g, Harlan Inc., Indianapolis, IN) were used in all experiments. After 1 week of acclimation to the animal facilities and behavioral test regimen, rats were randomly assigned to control, tail‐ and pelvic‐HLS groups (n = 6 or more per group). Experiments were performed in duplicate or triplicate. A total of 90 animals, 41 control, and 26 tail‐ and 23 belt HLS rats were studied. Body weights were measured at baseline and at 2 day intervals until euthanasia.
Rats were suspended in individual plastic cages for 2 weeks at about 30 degrees head‐down tilt. To set and adjust the suspension harness, rats were briefly (for 2–3 min) anesthetized by inhalation of isoflurane. After the animal had fully recovered from anesthesia, the angle of suspension was adjusted to make sure that when the animal is fully stretching its hindlimbs is unable to touch the ground.
Tail‐HLS was conducted as described previously (Chowdhury and Soulsby 2008; Chowdhury et al. 2011) using a tail harness constructed by looping a strip of Skin‐Trac orthopedic foam (Zimmer Inc., Charlotte, NC) around a pulley that can travel along a bar traversing the length of the cage. The adhesive surfaces of the reminder of the foam strip were applied to the long axis of the opposite sides of the tail, creating a “tail‐sandwich,” secured by enwrapping it with orthopedic stockinet and three one‐inch pieces of glass zip‐reinforced strapping tape at the base, middle, and few centimeters from the tip of the tail.
The pelvic support harness was made out of thick insulated copper wire (core diameter 1.5 mm and outer diameter 4 mm) molded in its center into the hoop‐like feature for securing a suspension string (SS) and bent as illustrated in the Figure 1 (right panel). The harness was adjusted to snugly, but without squeezing, follow the rat's body from the dorsum to the belly just in front of the rat's hips with lower arms (LA) of the harness fitting snuggly into the crease between the belly and respective inner thigh and folded back toward the main, central arc (CA) of the harness at the base of the tail following the rat's body curvature as closely as possible. In suspended position, the lower end of CA and front parts of LA provide most of the support to the rat's lower body against the force of gravity. Thus, these parts of the wire belt were wrapped with gauze‐padded polyester tubing (7 mm OD) helping to distribute a pressure over a larger wire‐body contact area, minimize chafing, and diminish possibility of rat body injury.
PPT values were determined at regular, 2–5 days intervals, with the final measurement being taken within 24 h of euthanasia. Dorsal hindlimb paw pressure pain withdrawal thresholds (PPT) were measured with a Randall–Selitto analgesia meter employing our standard laboratory technique (Romanovsky et al. 2006, 2010). Briefly, 10 determinations of PPT per animal (five per each hindlimb with an interval between sequential measurements greater than 10 min) were collected in each test session, filtered using mean ±1 SD cut‐off, averaged for both limbs and expressed in grams. Threshold force of linearly increasing pressure (~15 g/sec) was defined as a force that induces the first physical attempt of the animal to escape the stimulus. To avoid tissue injury the cut‐off force was set to 250 g of pressure. HLS rats were temporarily unsuspended, with harness remaining in place, for only for the periods of behavioral test trials (2–3 min per trial). In addition, food and water consumption were measured daily during the period of suspension in subset of experiments.
On the last day of the experiment, animal was deeply anesthetized with a mixture of ketamine and acyl promazine (10:1 v/v), at a dose of 2 mL/kg of body weight and euthanized by cardiac bleeding.
Bone mineral density measurements by dual energy X‐ray absorptiometry
Longitudinal bone densitometry was performed, using the Piximus Bone Densitometer (Lunar Corp., Madison, WI), to obtain measurements of bone mineral density (BMD) and bone mineral content (BMC) from the lumbar spine and proximal right tibia of each animal as described previously (Fluckey et al. 2006). Scans were performed under anesthesia for attachment of the suspension device on day 0, the day HS (or control housing) began and on day 14 immediately prior to euthanasia. Subsequently, the L1–L4 spine measurements were combined comprising mostly of trabecular bone. The tibia scans were divided into the proximal and distal one thirds, and the diaphyseal midshaft one third for analysis, to account for the changes in cancellous and cortical bone densities, respectively, as previously described (Fluckey et al. 2006). The precision and accuracy of the Piximus instrument have been determined by repeated measurements of five animals, five times each. In‐house precision analyses have been previously determined for adult rat femoral BMD to be 0.1% CV.
Radiographic analysis of spines following HLS
To determine the extent to which HLS induced curvature of the spine, whole‐body side X‐ray images of deeply anesthetized rats after suspension and prior to euthanasia were taken using an AXR minishot 110 X‐ray cabinet (Associated X‐ray Corporation, East Haven, CT) at 3 mA, 33 kV for 20 sec using Kodak X‐Omat TL film (Kodak, Rochester, NY) and processed on a Kodak X‐Omat RP automated film processor.
Blood collection and insulin analysis
Blood was collected by a ventricular puncture prior to euthanasia, plasma separated by centrifugation (5000g, 5 min), and stored at −20°C until further analysis of plasma Insulin levels using an Ultrasensitive Rat Insulin ELISA kit (Crystal Chem Inc., Downers Grove, IL), according to manufacturer's directions.
Following euthanasia, the right leg soleus muscles were isolated, and their wet weight was measured and expressed in relative units (mg per kg of body weight).
Statistical analysis was conducted using Statistica Software (StatSoft, Tulsa, OK) and Origin 9.0 Graphing and Analysis Software (OriginLab, Northampton, MA). The data were checked for normality of distribution (Shapiro–Wilk test) and analyzed using one‐ or two‐way analysis of variance (ANOVA), followed by Tukey's or Bonferroni's post hoc comparison tests. Best fit analysis of frequency distributions was conducted using a Levenberg–Marguardt algorithm of χ2 minimization (Origin, Microcal, Northampton, MA). During the fitting procedure all independent parameters of the fitted Boltzmann functions were allowed to vary. Effects were considered as statistically significant at P < 0.05. Data in figures are expressed as mean ± SE.
Radiographic analysis of the spine
We hypothesized that the pelvic method of HLS would create less change in mechanical load on the rat's lumbosacral skeleton because of greatly expanded distribution of a gravity (compressive) load of the belt, compared with tensile load from the base of the tail in tail‐HLS. To test this hypothesis, we used radiographic analysis by X‐ray and dual energy X‐ray absorptiometry (DEXA) images to measure and compare the thoracolumbar (Th‐L) and lumbosacral (L‐S) angles (analogous to Cobb's angles that measure a degree of kyphosis and lordosis in humans). The Th‐L and L‐S angles were defined as respective angles between Th8‐11 and L1‐4, and L1‐4 and S1‐3 segments of the spinal column (Fig. 2). In addition, the relative lumbar length (RLL) was measured between Th13 and S1 vertebrae, and normalized to pelvic girdle width (PW) measured at S1 vertebral level. The RLL and Th‐L angles were comparable between control and tail‐ and pelvic‐HLS rats (Fig. 2). However, supporting the concern regarding the deteriorating effect of tail‐HLS on the state of the rat axial skeleton, tail (but not pelvic)‐HLS was shown to result in a statistically significant decrease in the L‐S angle (Fig. 2F).
General characteristics (food, water, weight)
Changes in weight and food and water intake are indirect indicators of stress experienced by experimental animals. In our experiments, we did not observe any difference in food consumption between any of the groups of rats studied (Fig. 3A), although tail‐HLS demonstrated a slight but significant decrease in water consumption relative to control in the beginning of suspension period, Fig. 3B). Both HLS groups experienced statistically significant growth retardation. In fact, tail‐HLS rats even lost some weight (about 13 g) during first 3 days of HLS. Weight gain by suspended animals resumed during the second week of suspension but remained slower than that in control rats (Fig. 3C).
Muscle atrophy and bone loss
Disuse associated muscle atrophy and bone loss represent hallmark effects of lower limb musculoskeletal disuse in human bed‐ridden patients and space mission participants (Morey‐Holton and Globus 2002; Graebe et al. 2004). These changes are also well‐established consequences of rat HLS models (Morey‐Holton and Globus 2002; Morey‐Holton et al. 2005; Carpenter et al. 2010). In our experiments, we observed that both soleus muscle weight and tibial cancellous bone mineral density were decreased to the same degree after 2 weeks of either tail or pelvic suspension (Fig. 4). As an internal control, however, no changes in humerous density was detected in either of the HLS models during an experiment in the remaining loaded limbs (data not shown).
PPT and random plasma insulin concentration
To date, nociceptive changes have received relatively little attention in the HLS model. Recently, however, we provided the evidence of pressure hyperalgesia developing in tail‐HLS rats, as well as an indication that this could be associated with insulinopenia (Chowdhury et al. 2011). Here, we determined whether the PPT and associated insulinopenia was comparable in the tail‐HLS and the pelvic‐HLS animals. In these experiments, pressure hyperalgesia (decrease in PPT) developed to a similar degree after 2 weeks of either tail or pelvic suspension (Fig. 5A). Mean insulin measurements, however, demonstrated only a tendency to decrease from the control, to tail‐HLS and further to pelvic‐HLS groups of rats (Fig. 5B). Both PPT and insulin measurements are prone to high variability. This is specifically so for random insulin measures (fasted insulin was not analyzed as it may not represent conditions under which PPT was measured), considering that we did not control the time elapsed from the rat that was last eating prior to blood sampling. To circumvent this problem, we reanalyzed the data using the following approach. First, the PPT and insulin data that were collected at the end of experiment were filtered for outliers using mean ± 1 SD rule for each group of animals (control, tail‐, and pelvic‐HLS) separately. Then animals with both PPT and insulin measurements passing the filter test were selected for further study.
Analysis of filtered data measured in this way have confirmed previous findings (Chowdhury et al. 2011) of decreased PPT in groups of tail‐HLS animals, and demonstrate for the first time that both tail‐ and pelvic‐HLS rats have similarly decreased PPT (relative to control and relative to baseline PPT level, asterisks in Fig. 5C). Furthermore, this analysis revealed statistically significant differences of plasma insulin levels at euthanasia between control and either tail‐ or pelvic‐HLS rats (Fig. 5D). Finally, further analysis of insulin levels categorized into ranges of plasma concentrations suggested the existence of sigmoidal dose–response relationships between the plasma insulin level and PPT and body weight of studied animals, which could explain, in part, both the decrease in PPT and the prevention of weight gain in HLS rats (Fig. 6A and B, respectively).
This work confirms the results of previous studies (reviewed in Morey‐Holton et al. 2005) regarding the deleterious effects of short‐term HLS on body weight and postural muscle weight, and hindlimb bone mineral density. In addition, these findings confirm the recent observation (Chowdhury et al. 2011) of decreasing PPT of the hindlimb paw in HLS rats. The novel observations of this study are that despite sharply different effects of tail‐ and pelvic‐HLS techniques on mechanical loads experienced by the lower spine of the rat, the above mentioned effects of HLS developed similarly in both models. Another important result of our study is that it extends evidence for the development of subclinical insulinopenia in HLS animals (Hamburg et al. 2007; Chowdhury et al. 2011) with a possible link of this prediabetic state to the development of deep pressure hyperalgesia.
The tail‐HLS model is well a well‐established model of simulated microgravity (Morey‐Holton and Globus 2002; Morey‐Holton et al. 2005). The problem of lordosis (Fig. 2) in this model has been recognized for some time (Templeton et al. 1984; Wronski and Morey‐Holton 1987). However, it has not posed significant challenges prior to the measurement of pain thresholds being studied in tail‐HLS animals. Our finding of pressure hyperalgesia developing in tail‐suspended rats (Chowdhury et al. 2011) warranted a more detailed analysis of this issue, as lumbar stretch (increased tensile mechanical load to the spine) is considered as one of possible causes of low back pain in astronauts and bed‐ridden patients (Hutchinson et al. 1993; Styf et al. 2001; Carpenter et al. 2010). To address this we have compared here the tail‐ and newly developed pelvic‐suspension models of HLS.
Considering the purely technical aspects, when tail‐HLS was compared to the procedure of pelvic suspension, it is more labor consuming in its preparative period (pelvic belt manufacturing), but easier with regard to suspension procedure itself (placing the belt vs. tail harness) and has about the same success rate as measured by the duration of the rat remaining suspended through the entire 2 weeks of experiment. Only about 5% of rats in each group needed to be removed from experiment as repeatedly (more than once) requiring their harness to be reattached. By its design, the pelvic‐HLS does not carry the problem of tail harness placement – associated risk of impaired tail blood flow. However, we recognize that the state of pelvic belt support arm padding must be paid close attention to with wet or damaged padding being immediately replaced. None of pelvic‐HLS rats needed to be removed from these experiments because of inner thigh skin inflammation at the harness contact points. In our view, however, development of such inflammation may become a real problem in the experiments with longer than 2 weeks of suspension period.
Our current study demonstrated clearly different effects of the two suspension methods with regard to spinal lumbosacral curvature, which was more pronounced in the tail‐HLS than the pelvic‐HLS (Fig. 2). However, most of the other measured endpoints behaved similarly between two models of HLS. The exception was a decrease in water intake and net weight loss observed in the beginning of HLS period in tail‐HLS but not in pelvic‐HLS rats (Fig. 3B and C) suggesting a higher stress level in the tail‐HLS group (see Jacobsen et al. 2012). These differences, however, were transient. By the end of experiment, weight gain, food consumption, bone mineral density, soleus muscle mass, circulating insulin, or PPT levels were not distinguishable between two HLS models. Thus, we found no evidence of lumbosacral axial skeleton stretch as a factor in the pathologic etiology that develops during 2 weeks of HLS in the tail‐HLS rat model. However, it cannot be excluded that such tensile stretch might contribute to pathology in experiments with longer period of tail‐HLS.
The musculoskeletal deficiency of HLS rats in our study is comparable to that reported for tail‐HLS animals studied for the same time period (2 weeks of HLS) by other groups. Specifically, soleus muscle of our HLS rats weighted about 40% less than soleus muscle of age‐matched control rats (Fig. 4A), which is well in the range of 25–49% loss reported for male Wistar or SD rats soleus muscle after 2 weeks of tail‐HLS (Templeton et al. 1984; Somody et al. 1998; Picquet and Falempin 2003; Fujino et al. 2005; Mueller et al. 2005; Zhang et al. 2009).Our observed ~20% difference in bone mineral density in the proximal tibia of control and HLS rats (Fig. 4B) is also within the range of 8–21% effect of tail‐HLS on rat proximal tibia found in the literature (Bloomfield et al. 2002; Allen et al. 2006; Swift et al. 2010). Exact mechanisms of these effects of limb unloading are not known. It is tempting to speculate, however, that at least in part they may be associated with weakened activity of insulin/insulin‐like growth factor–1 (IGF‐1) axis in suspended rats. Both insulin and IGF‐1 are well known regulators of protein synthesis, bone, and muscle mass development (Davis et al. 1998; Thrailkill et al. 2005b; Han et al. 2007). Dysfunction of this control, associated with either decrease in circulating concentrations or peripheral insulin/IGF‐1 resistance occurs in healthy humans during space flight or prolonged bed rest and physical inactivity (Dolkas and Greenleaf 1977; Mikines et al. 1991; Tobin et al. 2002; Hamburg et al. 2007; Cree et al. 2010), and in skeletal muscles of tail‐HLS rats (Mondon et al. 1992; Stuart et al. 1993; Han et al. 2007). In the latter model, the decrease in circulating insulin (Nichols et al. 2008) and IGF‐1 (Perrien et al. 2007) was detected previously and confirmed with regard to insulin by us recently (Chowdhury et al. 2011) and in this study (Fig. 5). Our data also suggested existence of close relationships between the rat's body weight gain and random plasma insulin concentration, with 2.2 ng/mL of insulin as concentration required to achieve half‐maximal stimulation of weight gain (Fig. 5B). Interestingly, this value is very close to the 2.3 ng/mL insulin concentration required for half‐maximal activation of whole body amino acid disposal in young pigs (Davis et al. 1998). Another line of indirect support to the role of the insulin/IGF‐1 axis in the pathogenesis of musculoskeletal disuse conditions is that normal activity of this axis was shown as critical to keep the rate of protein degradation by ubiquitin‐proteasome pathway at a low level (Tischler et al. 1997; Wang et al. 2006). Hyperactivation of this pathway was identified as a cause of degradation of rat myosin heavy chain in muscles of astronauts (space shuttle flight [STS‐90]; Ikemoto et al. 2001). Accelerated protein degradation can also explain weight gain retardation, despite the preserved food intake in our HLS experiments (Fig. 3). Finally, muscle protein degradation and muscle wasting is accelerated in mouse models of insulin resistance and type 2 diabetes (Wang et al. 2006). Similarly, bone formation is impaired in rat and mouse models of type 1 and type 2 diabetes (Thrailkill et al. 2005a; Liu et al. 2007).
With regard to diabetes, our data provide further evidence demonstrating the remarkable phenotypic resemblance between HLS rats and the rat model of streptozotocin‐induced early type 1 prediabetes (STZ‐PD; Romanovsky et al. 2006, 2010). In both models, there is a moderate decrease in circulating insulin, which is not associated with changes in glucose metabolism (plasma glucose was not measured in this study, but was found normal in tail‐HLS rats in our previous work; Chowdhury et al. 2011), but appeared closely correlating with a decrease in PPT measured in same animals. “Insulin‐PPT” relationships could be fit with a sigmoidal curve in both models, except that best fit ED50 for an “insulin‐PPT” relationship to maintain normal pain threshold was lower in STZ‐ than in HLS‐rats (1.35 ± 0.06 vs. 1.8 ± 0.04 ng/mL, respectively; Fig. 5 in Romanovsky et al. 2006 and Fig. 6A, this work). Another difference between these models is weight gain, which was preserved at normal level in STZ‐PD, but suppressed in proportion to a degree of insulinopenia in animals in this study. The exact reason for these differences remains to be determined. They may, however, reflect differences of the models with respect to systemic insulin resistance. STZ‐PD rats have normal glucose tolerance (Romanovsky et al. 2004) demonstrating no signs of loss of skeletal muscle insulin sensitivity. The possibility of development of muscle insulin resistance in tail‐HLS rats was not addressed in this study. However, it has been reported in the literature (Mondon et al. 1992; Stuart et al. 1993; Han et al. 2007). If present in our HLS rats, it could explain higher insulin requirements for maintaining normal growth and PPT level seen in moderately insulinopenic and insulin resistant (HLS) rats as compared to insulinopenic but insulin sensitive STZ‐PD animals.
Tentative insulin dependence of evoked PPT observed in both STZ and HLS normoglycemic rats constitute an important issue on its own. Musculoskeletal pain is one of most prevalent symptoms of diabetic neuropathy (Dobretsov et al. 2010), which as most of other symptoms of this neuropathy, was traditionally attributed to neurotoxicity of diabetic hyperglycemia (Tomlinson and Gardiner 2008). The studies above clearly indicate that at least in some cases a direct effect of impaired insulin signaling, but not hyperglycemia, may serve as a pathogenic substrate for hyperactivity of deep muscle nociceptors. In humans, acute unloading the bodyweight results in a general increase of the withdrawal reflex excitability to prepare the limb in taking the first walking step (Serrao et al. 2012). This mechanism is, however, unlikely to add to pressure hyperalgesia in HLS rats, since it starts to develop only after about a week of HLS (Chowdhury et al. 2011). In a recent study, blood corticosterone level and hindlimb paw hypersensitivity to mechanical (von Frey hair) stimuli were observed increasing similarly in HLS rats and in rats that had tail suspension device attached but were not suspended (Tanaka et al. 2013). The authors had concluded that it is not microgravity or inactivity, but a restraint stress constitutes a major pathogenic factor determining changes in mechanical withdrawal thresholds in HLS‐rat. Although von Frey filament and paw pressure tests measure activity of different nociceptive pathways (skin vs. deep muscle nociceptors) and the relations between cortisol levels and nociception are not straightforward (Taylor et al. 1998; Benedetti et al. 2012; Jacobsen et al. 2012), our data do not allow us to exclude the possibility above. Further studies are needed to clarify the mechanisms of observed PPT changes and to establish their relevance (if any) to low back pain as a common comorbidity of space flight and prolonged bed rest in humans (Hutchinson et al. 1993; Styf et al. 2001; Carpenter et al. 2010).
In conclusion, these data show that HLS (by either tail‐ or pelvic‐suspension method) results in delay in the weight gain, skeleton–muscular deficiencies, and a mild prediabetic state with signs of exaggeration of evoked deep muscle pain. However, the increased tensile load on the lumbosacral spine in tail‐HLS plays little if any role in these pathological changes. Pelvic suspension appears as a suitable alternative to the tail‐HLS method in experiments with short‐term (2 weeks) rat hindlimb unloading. It remains to be determined if longer periods of HLS are sustainable with this technique.
The authors wish to acknowledge Nisreen Akel for performing the DEXA analyses and Dana Gaddy for reviewing the manuscript.
P.C. and M.D. conception and design of research; A.L., G.H., and M.E.S. performed experiments; A.L., G.H., M.E.S., and M.D. analyzed data; P.C. and M.D. interpreted results of experiments; M.D. prepared figures; P.C. and M.D. drafted manuscript; A.L., G.H., and M.E.S. edited and revised manuscript; P.C., A.L., G.H., M.E.S., and M.D. approved final version of manuscript.
Conflict of Interest
This work was supported by UAMS COM pilot grant program and a grant from Arkansas Space Grant Consortium (ASGC).
- Manuscript Received: April 23, 2013.
- Manuscript Revised: May 4, 2013.
- Manuscript Accepted: May 20, 2013.
- © 2013 The Authors. Physiological Reports published by Wiley Periodicals, Inc. on behalf of the American Physiological Society and The Physiological Society.
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