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Video Of Alexander Teplyashin’s Laboratory Lengthening Legs Of Sheep Using Stem Cell Implants

This is the 2nd video

There is some medical terms that can’t be translated like “stem cells” and “implant” so the video is quite accurate. Dr. Teplyashin is actually sort of a celebrity surgeon in the Moscow area. The rams/sheeps in the video are adult, so they are not going to get any taller. The implant goes into the bone after a small resection.

If you guys are interested in watching more videos about Teplyashin’s many video appearances on Russian Media TV , click here for the Youtube username Alexander Gaponov – https://www.youtube.com/user/elansky/videos

If any of you actually understands Russian, can you translate what they say in the short video?

Notice also in the video below how his lab follows general GLP (Good Laboratory Practices). This is not like what Gavrill Ilizarov did back in the 60s-80s with his version of leg lengthening.

I haven’t updated this website in a long time because I have recently started a new business venture. However, I promise that I will come back to this venture. There are other medical entrepreneurial ideas that I would like to pursue as well.

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Metacarpal growth to prove LSJL

Below I will submit evidence of LSJL.  It is not perfect proof but with the resources available it is not possible to generate perfect proof.

However, I will submit the following facts as evidence that there is a very strong possibility that LSJL works.

The basis on whether this is proof of LSJL depends on the answers to the following questions:

    • What is the probability that every bone shaft on my left side of the body is longer than the right except for the one metacarpal which I performed LSJL?
    • What is the probability that my LSJL loaded finger is longer likely due to lengthening of the metacarpal when everything on my left side is longer(can provide additional evidence of my left side being longer if needed)?


Is this not reasonable proof that LSJL works?


So the current hypothesis is that LSJL lengthened my right index finger metacarpal.  The right index finger metacarpal is about 1% longer than the left and since my left bones are almost universally longer than my right bones(at least for all the bones that I have identified) that probably means about a 2% growth(with 1% being a correction of the discrepency).  The remaining bones of the index finger may have grown as well but not beyond the initial discrepency.


Here are my two hand images.  If I could proof that the fourth and fifth metacarpals were longer on my left side on my right that would provide evidence that the fact the index finger metacarpal is longer on my right side is an outlier and is due to loading from LSJL.  The middle finger is not taking into account because it is close to where I loaded with LSJL so there might be some byproduct lengthening of the middle finger.

hand bones

Here’s a labeling of the bones of the hand.  It would be easy to measure if it was like but the bones are not that organized.


Here’s a labeling of the bones on an actual skeleton.  You can see how the hamate mucks up with an accurate measurement.


4th metacarpal5th metacarpal

From these images you can see how hard it is to get an accurate measurement of the 4th and 5th metacarpal.  The shaft of the fourth metacarpal is definitely longer on the left side and eyeballing the shaft of the the 5th metacarpal the left bone looks like a little bit longer.  In terms on the exact beginning and end of the bone it is hard to tell because of the hamate.

Here’s the left and right index finger:


frontal index metacarpals

The shaft of the right bone looks longer in addition to the overall bone being longer.

I submit that the fact that the fourth and fifth metacarpal all have the left shaft as longer than the right like all the other bones I have compared with the exception of the right and left metacarpals of the index finger of LSJL induced lengthening.

Another potential LSJL design mentioned in a scientist paper

Todd Dodge is a scientist who works at Hiroki Yokota’s lab which developed the beginnings of LSJL.  Most of the paper is not relevant to LSJL except for his data that compares the inside of the control bone and an axial loaded bone.  The difference in the cracks is not as dramatic as the control and LSJL loaded bone.    This indicates that LSJL may alter bone structure more dramatically than typical loading and hopefully in such a way that facilitates neo-growth plate formation.  The key takeaway is the sample LSJL device provided in the picture at the end of this article and in the appendix of Todd Dodge’s paper.

Experimental and Computational Analysis of Dynamic Loading for Bone Formation<-Link to thesis at end of article

This paper is written by Todd Dodge who works closely with Hiroki Yokota who was involved in the initial ideas behind LSJL.

“Curvature in the structure of bone was hypothesized to enhance its damping ability and lead to increased bone formation through bending. In addition, loading at frequencies near the resonant frequencies of bone was predicted to cause increased bone formation, specifically in areas that experienced high principal strains due to localized displacements during resonant vibration“<-Is there a specific frequency for cartilage formation?

“Many types of applied mechanical loading of the skeleton have been proposed as potential treatments for osteoporotic conditions, including whole body vibration, axial loading or bending of long bones, and lateral joint loading. Each mechanical loading modality is thought to strengthen bone by causing dynamic fluctuations in intramedullary fluid pressure in areas that experience enhanced stresses and strains due to the applied load. This dynamic pressure gradient{This dynamic pressure gradient may also lead to stem cells differentiating into chondrocytes to form neo-growth plates} may cause fluid flow through the lacunocanalicular network of pores in the bone, causing a shear stress to be applied to osteocytes that inhabit those pores and channels. This shear stress may excite the osteocytes, causing activation of osteoblast activity and initiation of the bone remodeling process. Mechanical loading may also lead to application of force directly to osteocytes as strain in the bone matrix changes the shape of the lacunae and canaliculae{plastic changes in the bone matrix could lead to permanent lengthening?}, imposing deformations on the osteocyte and its processes”

Todd Dodge used lateral knee loading on OVX rats.  1N of load was used at 5Hz for 5 min for a group of rats that was tail suspended.  Loading was done once a day for five straight days.  For a group of rats that were OVX 15Hz for 3 min for 10 days(5 days on, then one off)  12 week-old female sprague dawley rats.  So sort of medium along in the growing process with it starting to taper off.

“The slight increase in BMD in hindlimb-suspended mice may be attributed to additional mechanical stress being applied to the lumbar section of the body, possibly increasing bone growth in that area.”

Unfortunately longitudinal growth was not measured.

Here’s the tibia response to axial loading:


tibia load

Compare this to the LSJL holes which are much bigger between control and loaded and are larger.

“Future studies may incorporate not only cortical bone but also trabecular bone and growth plates, as well as surrounding tissues such as muscle, skin, and joints.”<-We may need to wait for further studies to get the results we need for LSJL.

“the e ffects of loading may not only be localized to nearby bones, but may have remote impacts in the spine.”

Here’s the knee loading device that he recommends, note though it is designed for BMD not for lengthening:

Knee Load device

Creep strength and it’s applications to LSJL

If LSJL can physically deform the bone then perhaps it can deform the bone in such a way as to make it longer.

Creep of trabecular bone from the human proximal tibia

“Creep is the deformation that occurs under a prolonged, sustained load and can lead to permanent damage in bone{So to get creep with LSJL the duration of the loads should be longer}. Creep in bone is a complex phenomenon and varies with type of loading and local mechanical properties. Human trabecular bone samples from proximal tibia were harvested from a 71-year old female cadaver with osteoporosis. The samples were initially subjected to one cycle load up to 1% strain to determine the creep load. Samples were then loaded in compression under a constant stress for 2 h and immediately unloaded. All tests were conducted with the specimens soaked in phosphate buffered saline with proteinase inhibitors at 37 °C. Steady state creep rate and final creep strain were estimated from mechanical testing and compared with published data. The steady state creep rate correlated well with values obtained from bovine tibial and human vertebral trabecular bone, and was higher for lower density samples. Tissue architecture was analyzed by micro-computed tomography (μCT) both before and after creep testing to assess creep deformation and damage accumulated. Quantitative morphometric analysis indicated that creep induced changes in trabecular separation and the structural model index. A main mode of deformation was bending of trabeculae{stretchinig of the trabeculae would be what would make it longer although it’s possible that bending would make trabeculae longer if done in a certain way}.”

” One manifestation of creep damage is the decreased stature of elderly individuals due to the creep damage of vertebrae”

” trabeculae from vertebral areas are mostly rod-like, while in the metaphyses and epiphyses of long bones there is a more balanced mixture of plate-like and rod-like trabeculae. Furthermore, it was shown that these cellular structures degrade differently during the progression of osteoporosis, resulting in differences in the degree of anisotropy of mechanical properties”

” Creep occurs in three stages: primary, secondary and tertiary. Primary creep is the brief initial period during which the creep rate decreases and is accompanied with some material relaxation. In secondary creep, which is the longest and most studied regime, a steady state creep rate (dε/dt) is observed. Tertiary creep, occurring at the end of the secondary regime, is associated with an accelerated creep rate and more damage accumulation that results in eventual failure if the load is sustained. If the creep test is stopped during the secondary stage and the load removed, there is some elastic and viscoelastic strain recovery.”

creep strain

“under a prolonged load, microcracking of the bone matrix (and not fracture of the whole trabeculae) was the primary mode of deformation during creep. On the other hand, it was shown that even a small damage, barely distinguished on radiographs, to older vertebrae accelerates creep, and leads to a visible contribution to a vertebra deformity”

Here’s a paper that shows possible positive benefits of creep deformation:

In vitro torsion-induced stress distribution changes in porcine intervertebral discs.

“A cadaveric porcine spine motion segment experiment was conducted.

To test the hypothesis that small vertebral rotations cause increased stress in the anulus while decreasing stress in the nucleus through stiffening of the anulus.

Stress profiles of the intervertebral disc reportedly depend on degeneration grade and external loading. Increased stress in the anulus was found during asymmetric loading. In addition, depressurization of the nucleus combined with an instantaneous disc height increase was found when small (<2 degrees ) axial vertebral rotations were applied{So twisting could increasing height?}.

vertebral rotation

Seven lumbar porcine cadaveric motion segments consisting of two vertebrae and the intervening disc with ligaments were loaded in the neutral position with 340 N of compression. Stress profiles were obtained in the neutral position, then after 0.5 degrees and 1 degrees axial rotation of the bottom vertebral body. The distribution of compressive stress in the disc matrix was measured by pulling a miniature pressure transducer through the disc along a straight path in the midfrontal plane. Stress profiles were measured in vertical (0 degrees ) and horizontal (90 degrees ) orientation.

Deformation of the anulus by small axial rotations of the lower vertebra instantaneously decreased the horizontally and vertically measured stress in the nucleus while increasing stress in the anulus. A 1-hour period of creep loading decreased the stresses in the nucleus and the anulus 20% to 30%, depending on the orientation, but the effect of an increasing stress in the anular region after axial rotation persisted.

The compressive Young’s modulus of the composite anulus tissue increases instantaneously when small axial rotations are applied to porcine spine motion segments. This is accompanied by decreased stress in the nucleus pulposus, increased stress in the anulus fibrosus, changes in the stress profile superimposed on and independent of prolonged viscoelastic creep and dehydration, and changes in stress distribution independent of horizontal and vertical orientation.”

“the nucleus acts as a sealed hydraulic system, in which the fluid pressure rises substantially when volume is increased (by fluid injection) and falls when volume is decreased (by surgical excision or endplate fracture). “Stress” peaks in the anulus reportedly are increased by prior loading and degeneration.”

“[The] pressure reduction in the nucleus pulposus under torsion coincided with an increase of disc height ”

Magnitude of loads influences the site of failure of highly curved bones.

“The structure and material properties of bones along with applied boundary conditions determine the region of peak stresses, where fracture is expected to occur. As the site of peak stresses is not influenced by the magnitude of applied load, the fracture site is not expected to change during fatigue loading of whole bone at different loads. However, in a highly curved bone such as the rat ulna, the magnitude of applied loads was found to influence the fracture site. Fatigue loading was conducted under load control on intact rat forearms and on excised ulnae. The distance to the site of failure from the proximal olecranon process of ulnae was determined. In intact forearms, the site of failure demonstrated a linear progression distally, towards sites with lower moment of inertia (or sites exhibiting lower section modulus). Intact rat forearms and excised ulnae loaded to failure at low loads fractured 2-3mm distal to where they failed when applying high loads. This indicates a shift in the site of failure by approximately 10% of whole bone length just by varying the applied load magnitude. The site of failure in excised ulnae was similar when loading at 2Hz or at 4Hz, suggesting that this was frequency independent in this range and indicating that strain rate was not an important contributing factor. Creep loading of excised ulnae also demonstrated similar changes in the site of failure, indicating that magnitude of loads, and not type of loading were important in determining the site of failure.”

“the shape of whole bone can be such that failure occurs at sites other than the smallest cross-section and/or smallest moment of inertia. This is especially true for curved bones such as the ulnae and tibiae of commonly used rodent strains.”

“Loading was conducted by placing the excised ulnae between brass U-cups, with the load being applied in the direction parallel to the length of the ulna (left-to-right). During this loading, the natural curvature of the ulna causes bending induced tensile and compressive stresses on the lateral and medial surfaces, respectively”

“a gradual shift is observed as the site of failure of the ulna moves from 15.2 mm to 17.3 mm as the peak compressive load decreases from 26 N to 14 N”

“In excised ulnae, the site of failure shifted distally as the load was decreased, with failure occurring slightly distal to the mid-shaft at high loads and even more distally at lower loads, irrespective of the frequency of cyclic loading (2 Hz or 4 Hz) or the mode of loading (creep or cyclic).”

“Failure occurred at extremely short time scales at high loads, and at considerably longer time scales when loading at low loads. When loading at high loads, times to failure were not dependent on loading frequency or mode of loading (creep or cyclic). When loading at low loads, the time it took for the bones to fail decreased with increased frequency of cyclic loading  and was the shortest during creep loading. Dring cyclic loading, failure occurs in fewer cycles at greater loads, irrespective of the frequency of loading. At the same loads, loading at a higher frequency (2 Hz vs 4 Hz), there was no difference in the numbers of cycles to failure when loading was conducted at different frequencies (2 Hz or 4 Hz).”

“As expected, loading at high loads causes bones to fail in shorter times (within 30 s) as opposed to loading at low loads (periods of a week or two).”<-Loading for a week or two would be extreme.

I’m Writing A Book

I am currently working on writing a book that summarizes EVERYTHING that is on this website. All the important things will be added, and the extraneous information will not be. I will mention all the research and work that has been attempted in the last 15 years, from Sky, to Tyler, to Hakker, to Tim, and others who have tried to help out.

That is why I will not be posting on this website for at least another 4-6 months.

In addition, I have to focus on two other different businesses which are my primary sources of income.

  • Most of my time in the day is devoted to my companies and earning money, and keeping fit.
  • Most of my time at night will be devoted to finishing this book, as well as caring for my family members.

When the book is finally finished, probably in 2016, it will be released to the world, and this website will be transformed into something completely different.

I have decided to use the Natural Height Growth as one of the brand names under my primary umbrella corporation, and treat this website as a real asset. I will be coming back to make good on my promise to push the research much further.

This website will keep on going, and I will try to clean things up, and change dead links, and similar maintenance stuff now.

Anything new that comes out in the next few months will be from Tyler.

Resveratrol for height growth

I wrote about Resveratrol before and it is available for sale.

Resveratrol Supplementation Affects Bone Acquisition and Osteoporosis: Pre-Clinical Evidence Towards Translational Diet Therapy.

“Osteoporosis is a major public health issue that is expected to rise as the global population ages. Resveratrol (RES) is a plant polyphenol with various anti-aging properties. RES treatment of bone cells results in protective effects, but dose translation from in vitro studies to clinically relevant doses is limited since bioavailability is not taken into account. The aims of this review is to evaluate in vivo evidence for a role of RES supplementation in promoting bone health to reduced osteoporosis risk and potential mechanisms of action. Due to multiple actions on both osteoblasts and osteoclasts, RES has potential to attenuate bone loss resulting from different etiologies and pathologies. Several animal models have investigated the bone protective effects of RES supplementation. Ovariectomized rodent models of rapid bone loss due to estrogen-deficiency reported that RES supplementation improved bone mass and trabecular bone without stimulating other estrogen-sensitive tissues. RES supplementation prior to age-related bone loss was beneficial. The hindlimb unloaded rat model used to investigate bone loss due to mechanical unloading showed RES supplementation attenuated bone loss in old rats, but had inconsistent bone effects in mature rats. In growing rodents, RES increased longitudinal bone growth, but had no other effects on bone. In the absence of human clinical trials, evidence for a role of RES on bone heath relies on evidence generated by animal studies.”

“Resveratrol (RES) is a polyphenolic (3,4’,5-trihydroxystilbene) compound naturally present in red wine and a variety of plant foods such as grapes, cranberries, and nuts”

” human bone marrow-derived MSC with RES increased gene expression of the key osteogenic transcription factors, Runx2 and Osterix. RES was also demonstrated in vitro to act on various signal transduction pathways. RES activated the estrogen-mediated extracellular signal-regulated kinase 1/2 (ERK) signaling pathway regulating osteoblast differentiation and proliferation.  RES activated AMP-activated protein kinase (AMPK) which regulates osteoblast differentiation and inhibits bone resorption by acting as a negative regulator of RANKL. RES augmented Wnt signaling which stimulated osteoblastogenesis and bone formation. Treating human bone marrow-derived MSC with RES promoted differentiation of MSC towards osteoblasts by up-regulating Runx2 gene expression through the activation of Sirt1. Also, activation of Sirt1 by RES was shown to promote binding to PPARγ which repressed MSC differentiation into adipocytes. Additionally, RES suppresses osteoclastogenesis by acting through Sirt1 to bind to RANK which inhibited binding to RANKL”<-many of these processes should impact longitudinal bone growth as well.

Resveratrol stimulated tibial and vertabral length in new zealand white rabbits that were 12 weeks old.  200mg per kg of bodyweight were given.  Increased the amount of chondrocytes in the tibia and stimulated growth plate area while reducing fusion.  Decreased vascularization indicated by lower VEGF and laminin levels.

“RES supplementation delayed growth plate fusion by suppressing the replacement of avascular cartilage with vascularized bone indicated by the down-regulated gene expression of vascular endothelial growth factor, a signaling molecule in vascularization, and laminin, a cartilage protein.”

In 6 month old Fisher-Brown Norway rats, it increased tibia length and width.  Dosage was 12.5mg per kg of bodyweight.

“In vitro, RES treatment of chondrocytes obtained from an adult rat femur protected against the catabolic effect of pro-inflammatory cytokine, interleukin-1β”